US20090286008A1 - Laser-produced porous surface - Google Patents

Laser-produced porous surface Download PDF

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Publication number
US20090286008A1
US20090286008A1 US12/386,679 US38667909A US2009286008A1 US 20090286008 A1 US20090286008 A1 US 20090286008A1 US 38667909 A US38667909 A US 38667909A US 2009286008 A1 US2009286008 A1 US 2009286008A1
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Prior art keywords
layer
laser
powder
metal powder
titanium
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US12/386,679
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US8268099B2 (en
Inventor
William O'Neill
Christopher J. Sutcliffe
Eric Jones
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University of Liverpool
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Howmedica Osteonics Corp
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Application filed by Howmedica Osteonics Corp filed Critical Howmedica Osteonics Corp
Priority to US12/386,679 priority Critical patent/US8268099B2/en
Publication of US20090286008A1 publication Critical patent/US20090286008A1/en
Priority to US12/843,376 priority patent/US8268100B2/en
Assigned to HOWMEDICA OSTEONICS CORP. reassignment HOWMEDICA OSTEONICS CORP. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: JONES, ERIC, O'NEILL, WILLIAM, SUTCLIFFE, CHRISTOPHER J.
Priority to US13/605,354 priority patent/US8992703B2/en
Application granted granted Critical
Publication of US8268099B2 publication Critical patent/US8268099B2/en
Assigned to THE UNIVERSITY OF LIVERPOOL reassignment THE UNIVERSITY OF LIVERPOOL CONFIRMATORY ASSIGNMENT OF 50% INTEREST FOR HOWMEDICA OSTEONICS CORP. AND 50% INTEREST FOR THE UNIVERSITY OF LIVERPOOL. Assignors: HOWMEDICA OSTEONICS CORP.
Priority to US14/671,545 priority patent/US10525688B2/en
Priority to US16/690,307 priority patent/US11155073B2/en
Priority to US17/176,842 priority patent/US11186077B2/en
Priority to US17/401,977 priority patent/US11510783B2/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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    • B22F7/002Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression of porous nature
    • B22F7/004Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression of porous nature comprising at least one non-porous part
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
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    • B23K26/382Removing material by boring or cutting by boring
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
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    • B29WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
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    • B29C64/153Processes of additive manufacturing using only solid materials using layers of powder being selectively joined, e.g. by selective laser sintering or melting
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    • BPERFORMING OPERATIONS; TRANSPORTING
    • B22CASTING; POWDER METALLURGY
    • B22FWORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
    • B22F2301/00Metallic composition of the powder or its coating
    • B22F2301/20Refractory metals
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B22CASTING; POWDER METALLURGY
    • B22FWORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
    • B22F2301/00Metallic composition of the powder or its coating
    • B22F2301/20Refractory metals
    • B22F2301/205Titanium, zirconium or hafnium
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B22CASTING; POWDER METALLURGY
    • B22FWORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
    • B22F2301/00Metallic composition of the powder or its coating
    • B22F2301/35Iron
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B22CASTING; POWDER METALLURGY
    • B22FWORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
    • B22F2999/00Aspects linked to processes or compositions used in powder metallurgy
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2101/00Articles made by soldering, welding or cutting
    • B23K2101/34Coated articles, e.g. plated or painted; Surface treated articles
    • B23K2101/35Surface treated articles
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2103/00Materials to be soldered, welded or cut
    • B23K2103/02Iron or ferrous alloys
    • B23K2103/04Steel or steel alloys
    • B23K2103/05Stainless steel
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2103/00Materials to be soldered, welded or cut
    • B23K2103/08Non-ferrous metals or alloys
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2103/00Materials to be soldered, welded or cut
    • B23K2103/08Non-ferrous metals or alloys
    • B23K2103/14Titanium or alloys thereof
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2103/00Materials to be soldered, welded or cut
    • B23K2103/18Dissimilar materials
    • B23K2103/26Alloys of Nickel and Cobalt and Chromium
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K2103/00Materials to be soldered, welded or cut
    • B23K2103/50Inorganic material, e.g. metals, not provided for in B23K2103/02 – B23K2103/26
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02PCLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
    • Y02P10/00Technologies related to metal processing
    • Y02P10/25Process efficiency

Definitions

  • the present invention relates to a porous surface and a method for forming the same, which uses a directed energy beam to selectively remelt a powder to produce a part.
  • this invention relates to a computer-aided laser apparatus, which sequentially remelts a plurality of powder layers to build the designed part in a layer-by-layer fashion.
  • the present application is particularly directed toward a method of forming a porous and partially porous metallic structure.
  • the selective laser remelting and sintering technologies have enabled the direct manufacture of solid or dense three-dimensional articles of high resolution and dimensional accuracy from a variety of materials including wax, metal powders with binders, polycarbonate, nylon, other plastics and composite materials, such as polymer-coated metals and ceramics.
  • the metal articles formed in these ways have been quite dense, for example, having densities of up to 70% to 80% of fully dense (prior to any infiltration).
  • Prior applications of this technology have strived to increase the density of the metal structures formed by the remelting or sintering processes.
  • the field of rapid prototyping of parts has focused on providing high strength, high density, parts for use and design in production of many useful articles, including metal parts.
  • the present invention relates to a method for producing a three-dimensional porous structure particularly for use with tissue ingrowth.
  • a layer of metallic powder is deposited onto a substrate or a build platform.
  • Preferred metals for the powder include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
  • a laser beam with predetermined settings scans the powder layer causing the powder to preferentially remelt and consequently solidify with a decreased density, resulting from an increase in porosity as compared to a solid metal.
  • the range of the laser's power may be between 5 W and 1000 W.
  • successive offset layering and remelting are continued until the porous part has been successfully completed.
  • the benefit of the part formed is that that decreased density increases porosity thus enabling the part to be used for, among other things, tissue ingrowth.
  • the first layer of metallic powder is deposited onto a solid base or core and fused thereto.
  • Preferred metals used for the core include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium.
  • Successive powder layers of the same or different materials are once again added in a layer-by-layer fashion until the part is completed.
  • This embodiment has the desired effect of providing a structure in which the porosity may be increased as the structure is built, resulting in a graded profile in which the mechanical properties will also be reduced outwards from the core. This will allow the formed part to be used for, among other things, medical implants and prosthesis, but yet still include a surface for tissue ingrowth.
  • the method of producing a three-dimensional porous tissue ingrowth structure may include depositing a first layer of a powder made from a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, onto a substrate. Followinged by scanning a laser beam at least once over the first layer of powder.
  • the laser beam having a power (P) in Joule per seconds with a scanning speed (v) in millimeters per second with a range between 80 and 400 mms. and a beam overlap (b) in millimeters of between 50% and ⁇ 1200%.
  • P power
  • v scanning speed
  • b beam overlap
  • At least one additional layer of powder is deposited and then the laser scanning steps for each successive layer are repeated until a desired web height is reached.
  • at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
  • the thickness of the first layer and said successive layers of powder is between 5 ⁇ m-2000 ⁇ m.
  • the laser can be applied either continuously or in a pulse manner, with the frequency of the pulse being in the range of approximately 1 KHz to 50 KHz.
  • the method is carried out under an inert atmosphere, more preferably specifically an Argon inert atmosphere.
  • a third metal may be used to act as an intermediate.
  • the third metal would act as a bond coat between the core and first layer of powder.
  • the core may be integral with the resultant porous ingrowth structure and impart additional physical properties to the overall construct.
  • the core may also be detachable from the resultant porous surface buildup.
  • FIG. 1 is a diagrammatic illustration of the apparatus used to make test samples according to the processes of the present invention
  • FIG. 2 is a photographic image showing an array of samples produced by the processes as performed by the apparatus of FIG. 1 ;
  • FIG. 3 is a table showing a series of parameters used for the samples of FIG. 2 ;
  • FIGS. 4 to 10 are scanning electron microscope images of the surface structure of various samples made by the method according to the invention.
  • FIG. 11 is a scanning electron microscope micrograph taken from a porous Ti sintered structure
  • FIG. 12 is an optical image of a section through a sample showing the microstructure
  • FIG. 13 is an image detailing surface structures
  • FIGS. 14 and 15 are non-contact surface profilimetry images detailing plan views of the samples.
  • FIGS. 16 to 25 are scanning electron microscope micrographs produced prior to multi-layer builds shown in FIGS. 7 and 8 .
  • FIG. 26 indicates the metallography and spectra of a typical bond coat structure.
  • FIG. 27 shows the effect of line spacing on pore size.
  • FIG. 28 a - f are examples of typical waffle structures.
  • FIG. 29 is a trabecular bone-type structure constructed from a micro CT scan.
  • FIG. 30 shows typical freestanding structures.
  • FIG. 31 shows a freestanding structure built using the preferred scanning strategy.
  • the present invention relates to a method of forming porous and partially porous metallic structures which are particularly but not exclusively applicable for use in hard or soft tissue interlock structures for medical implants and prosthesis.
  • the method makes use of laser technology by employing a variety of scanning strategies.
  • Typical metal and metal alloys employed include stainless steel, cobalt chromium alloys, titanium and its alloys, tantalum and niobium, all of which have been used in medical device applications.
  • the present invention can be used for such medical device applications where bone and soft tissue interlock with a component is required, or where a controlled structure is required to more closely match the mechanical properties of the device with surrounding tissue. Additionally, the present invention may be employed to enhance the biocompatibility of a porous structure with animal tissue. With these advantages in mind, a structure may be created using specific dimensions required to accommodate a particular patient.
  • One particular intention of the present invention is to produce a three-dimensional structure using a direct laser remelt process, for example, for building structures with or without a solid base or core.
  • the three-dimensional structure could be used to provide a porous outer layer to form a bone in-growth structure.
  • the porous structure when applied to a core, could be used to form a prosthesis with a defined stiffness to both fulfill the requirement of a modulus match with surrounding tissue and provide interconnected porosity for tissue interlock.
  • a further use could be to form an all-porous structure with grade pore size to interact with more than one type of tissue.
  • the process can be used to build on a solid base or core with an outer porous surface, the porosity of which is constant or which varies.
  • the base or core materials to which the process is applied is either titanium and its alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
  • the preferred surface coatings are titanium, cobalt chrome and tantalum but both stainless steel and niobium can also be used.
  • Fully porous structures may be built from any of the materials tested, with the preferred material being titanium.
  • One intention of the present invention is to produce a method which can be exploited on a commercial basis for the production of, for example, bone interlock surfaces on a device although it has many other uses.
  • a method of forming a three-dimensional structure includes building the shape by laser melting powdered titanium and titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
  • the laser may be a continuous wave or pulsed laser beam.
  • the method can be performed so that the structure is porous and if desired, the pores can be interconnecting to provide an interconnected porosity.
  • the method can include using a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum, on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam.
  • a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam.
  • a mixture of desired mixed materials may be employed.
  • the method can be applied to an existing article made from cobalt chrome, titanium or titanium alloys, stainless steel, tantalum or niobium, such as an orthopedic implant, to produce a porous outer layer from any of the aforementioned metals or alloys to provide a bone in-growth structure.
  • a cleaning operation to ensure a contaminant-free surface may be employed prior to the deposition of any powder onto a substrate.
  • this process may include a solvent wash followed by a cleaning scan of the laser beam without the presence of particles.
  • a coating process may be employed.
  • the coating process includes applying a third metal directly to the substrate, which has a higher bond strength to the substrate then does the first layer of powder. This process is particularly useful when the substrate and first powder layer are of different materials.
  • the process of coating the substrate may be accomplished using known processes including laser deposition, plasma coating, cold gas dynamic spraying or similar techniques.
  • One example of the coating process includes using either niobium or tantalum as an interface between a cobalt chrome alloy substrate and a first layer of titanium powder.
  • the present invention can also include a laser melting process, which precludes the requirement for subsequent heat treatment of the structure, thereby preserving the initial mechanical properties of the core or base metal.
  • the present invention may be applied to produce an all-porous structure using any of the aforementioned metal or metal alloys.
  • Such structures can be used as finished product or further processed to form a useful device for either bone or soft tissue in-growth. Additionally, the structure may be used to serve some other function such as that of a lattice to carry cells.
  • the pore density, pore size and pore size distribution can be controlled from one location on the structure to another. It is important to note that successive powder layers can differ in porosity by varying factors used for laser scanning powder layers. As for example, a first layer of powder is placed and subsequently scanned. Next a second layer of powder is placed and scanned. In order to control porosity the second scan may be angled relative to the first scan. Additionally, the angling of the scanning as compared to previous and post scans may be maneuvered and changed many times during the process of building a porous structure. If a structure was built without alternating the angling of any subsequent scans you would produce a structure having a plurality of walls rather than one with an interconnecting or non-interconnecting porosity.
  • the laser melting process includes scanning the laser beam onto the powder in parallel scan lines with a beam overlap i.e., scan spacing, followed by similar additional scans or subsequent scans at 90°.
  • the type of scan chosen may depend on the initial layer thickness as well as the web height required.
  • Web height refers to the height of a single stage of the porous structure. The web height may be increased by deposited additional layers of powder of a structure and scanning the laser at the same angle of the previous scan.
  • the additional scan lines may be at any angle to the first scan, to form a structure with the formation of a defined porosity, which may be regular or random.
  • the scan device may be programmed to proceed in a random generated manner to produce an irregular porous construct but with a defined level of porosity.
  • the scan can be pre-programmed using digitized images of various structures, such as a trabecular bone, to produce a similar structure. Contrastingly, the scan may be pre-programmed using the inverse of digitized images, such as the inverse of a digitized trabecular bone to produce trabecular shaped voids.
  • Many other scanning strategies are possible, such as a waffle scan, all of which can have interconnecting porosity if required.
  • the beam overlap or layer overlap may be achieved by rotation of the laser beam, the part being produced, or a combination of both.
  • a first method according to the present invention is intended to produce a porous structure for bone in-growth on the outer surface layer of a prosthesis.
  • the nature of the material formed as a result of laser melting of powdered beads is principally dependent on the thermal profile involved (heating rate, soaking time, cooling rate); the condition of the raw material (size and size distribution of powder particles); atmospheric conditions (reducing, inert or oxidizing chamber gas); and accurate control of the deposited layer thickness.
  • optimum porosity is between approximately 20% and 40%, and aim to mid value with a mean volume percent of voids of about 70%.
  • the preferred pore structure is irregular and interconnected, with a minimum pore size between about 80 ⁇ m and 100 ⁇ m and a maximum pore size between 80 ⁇ m and 800 ⁇ m.
  • the structured thickness for in-growth is 1.4-1.6 mm, but can be larger or smaller depending on the application. As for example, it may be necessary to produce even smaller pore sizes for other types of tissue interaction or specific cellular interaction.
  • the first phase of development of the present invention involved an investigation, designed to characterize the material transformation process and to identify the optimum parameters for processing using three substrate materials CoCr and Ti stainless steel alloys, with five powder types Ti, CoCr, Ta and Nb, stainless steel.
  • FIG. 1 there is shown the apparatus used to carry out the method which comprises an Nd; YAG industrial laser 10 manufactured by Rofin Sinar Lasers, in Hamburg, Germany, integrated to an RSG1014 analogue galvo-scanning head 12 providing a maximum scan speed of 500 mm/s.
  • the laser beam 14 is directed into an atmospherically controlled chamber 16 , which consists of two computer-controlled platforms for powder delivery and part building.
  • the powder is delivered from a variable capacity chamber 18 into the chamber 16 and is transported by a roller 20 to a build platform 22 above a variable capacity build chamber 24 .
  • the build and delivery system parameters are optimized for an even 100 ⁇ m coating of powder to be deposited for every build layer.
  • the metals chosen as surface materials are all difficult to process due to their affinity for oxygen. Cr and Ti are easily oxidized when processed by laser in oxygen-containing atmosphere, their oxide products have high melting points and poor flowability. For this reason, and to prevent the formation of other undesirable phases, the methods were carried out under an Argon inert atmosphere in chamber 16 . Pressure remained at or below atmospheric pressure during the entire application.
  • the build chamber 24 illustrated in FIG. 1 and method of layering described above is suitable for test specimens and constructs such as three-dimensional freestanding structures.
  • an existing device such as acetabular metal shells, hip and knee femoral components, knee tibial components and other such devices, considerable changes to the powder laying technique would need to be applied.
  • Co212-e Cobalt Chrome alloy was used.
  • the CoCr was configured into square structures, called coupons. Arrays of CoCr coupons were built onto a stainless steel substrate.
  • the Co212-e Cobalt Chrome alloy had a particle size distribution of 90 ⁇ 22 um, i.e., 90% of the particles are less than 22 ⁇ m, the composition of which is shown in the table below.
  • An array of nine sample coupons were produced as shown in FIG. 2 , with the process of Table 2, using a maximum laser power of 78 watts (W) and laser scanning speed for each coupon varying between 100-260 mms ⁇ 1 .
  • W maximum laser power
  • a higher laser power may be employed; however, a higher laser power would also necessitate increasing the speed of the laser scan speed in order to produce the desired melting of the powder layer.
  • a simple linear x-direction scan was used on each of the coupons. This allowed the processing parameter, beam overlap, to be used to control the space between successive scan lines. That is, with a 100 ⁇ m laser spot size, an overlap of ⁇ 200% produces a 100 ⁇ m gap between scans.
  • the acceptable range for the beam overlap is given at +50% to ⁇ 1200% it should be duly noted that the negative number only refers to the fact the there is a gap as opposed to a beam overlap between successive scans. For instance a beam overlap of zero refers to the fact that successive scans on the same layer of powder border each other. If the beam overlap was 5% then 5% of the first scan is overlapped by the second scan. When computing the Andrew number the absolute value of the beam overlap is used. The complete set of process parameters used is shown in Table 2 below.
  • CoCr was the first of four powders to be examined and, therefore, a wide range of process parameters was used. In each case, laser power and the pulse repetition rate were kept constant, i.e., continuous laser pulse, to allow the two remaining parameters to be compared. Layer thickness was maintained at 100 ⁇ m throughout all the experiments described here. Layer thickness can, however, vary between 5 ⁇ m to 2000 ⁇ m.
  • the particle size description was 80% ⁇ 75 ⁇ m at a purity of 99.85%. Due to its higher melting temperature compared to that of CoCr (Nb being at about 2468° C., and CoCr being at about 1383° C.), the laser parameters used included a reduced scanning speed range and increased beam overlap providing increased specific energy density at the powder bed. In addition, the pulse repetition rate was varied from 20 kHz to 50 kHz.
  • Tantalum used in this study had a particular size distribution of 80% ⁇ 75 ⁇ m with a purity of 99.85%.
  • Ta has a melting point of about 2996° C. and was processed using the same laser parameters as Nb. Now confident of the atmospheric inertness, the Ta powder was melted directly onto the CoCr and Ti substrates.
  • Bio-medical alloys of Titanium were not readily available in powder form and so pure Ti was chosen.
  • the particle size distribution for the Ti powder was 80% ⁇ 45 ⁇ m with a purity of 99.58%.
  • the same parameters used for Nb and Ta were also used for the Ti powder.
  • Ti has a lower melting point than Ta or Nb, Ti being at about 1660° C., but has a higher thermal conductivity than Ta or Nb. This implies that although the powder should require less energy before melting, the improved heat transfer means a larger portion of the energy is conducted away from the melt pool.
  • FIG. 5 is an image of two coupons produced from a CoCr array on Ti alloy substrates. This array was chosen because it best satisfied the requirements of this exercise. The parameters were: laser power of 82 W continuous wave (cw); 25% beam overlap; scanning speed varied from 100 mms ⁇ 1 to 260 mms ⁇ 1 in 20 mm ⁇ 1 increments; the images of the coupons shown here, taken from this array, were produced with scanning speeds of 180 mms ⁇ 1 to 200 mms ⁇ 1 .
  • the surface is comprised of fused pathways that develop a network of interconnected pores. This structure continues throughout the layer until the interface is reached.
  • the interface is characterized by a patchwork of fusion bonds. These bond sites are responsible for securing the interconnected surface structure to the baseplate.
  • the macroscopic structure is covered with unmelted powder particles that appear to be loosely attached.
  • FIGS. 6 and 7 are the scanning electron microscope images produced from the Nb and Ta coupons on Ti alloy substrates.
  • FIGS. 6( a ) to 6 ( e ) are scanning election microscope images of the surface structure of Nb on Ti alloy substrates, produced with a laser power of 82 W cw, ⁇ 40% beam overlap.
  • the scanning speeds used were: 160 mms ⁇ 1 for FIG. 6( a ), 190 mms ⁇ 1 for FIG. 6( b ), 200 mms ⁇ 1 for FIG. 6( c ), 210 mms ⁇ 1 for FIG. 6( d ) and 240 mms ⁇ 1 for FIG. 6( e ), respectively.
  • FIGS. 7( a ) to 7 ( c ) are scanning election microscope images of the surface structure of Ta on Ti alloy substrates produced using the same parameters used in the Nb or Ti alloy substrates except: FIG. 7( a ) was produced with a scanning speed of 160 mms ⁇ 1 ; FIG. 7( b )'s speed was 200 mms ⁇ 1 and FIG. 7( c )'s speed was 240 mms ⁇ 1 , respectively.
  • An increased beam overlap was used here as Nb and Ta have high melting points, which require a greater energy density.
  • the surfaces once again exhibit significant levels of unmelted powder particles and loosely attached resolidified beads that vary in size from a few microns to several hundred microns. All samples were loosely brushed after completion and cleaned in an ultrasonic aqueous bath. It is possible that further cleaning measures may reduce the fraction of loose particles.
  • FIGS. 8( a ) to 8 ( e ) are scanning electron microscope images taken from the Ti coupons on the CoCr alloy substrates.
  • the laser processing parameters used were the same as those for the Nb and Ta powders, with once again only the speed varying.
  • the scanning speed was varied from 160 mms ⁇ 1 ( FIG. 8( a ), 170 mms ⁇ 1 ( FIG. 8( b )), 200 mms ⁇ 1 ( FIG. 8( c )); 230 mms ⁇ 1 ( FIG. 8( d ) to 240 mms ⁇ 1 ( FIG. 8( e )).
  • the Ti coupon on CoCr samples, FIGS.
  • 8( a ) to 8 ( c )) indicate very high density levels compared to the other examples.
  • the line-scans can be clearly seen, with good fusion between individual tracks, almost creating a complete surface layer. The surface begins to break up as the scanning speed is increased.
  • FIGS. 9( a ) to 9 ( e ) are scanning electron microscope images of surface structures of Ti on Ti alloy substrates produced with the same parameters used in FIGS. 8( a ) to 8 ( e ), respectively. It is unclear why Ti should wet so well on CoCr substrates. In comparison, Ti on Ti exhibits similar characteristic patterns as with Nb, Ta, and CoCr, specifically, an intricate network of interconnected pores.
  • the scanning speed, 160 mms ⁇ 1 and the laser power 72 W cw were kept constant while the beam overlaps; ⁇ 400% in FIGS. 10( a ) and 10 ( b ); ⁇ 500% in FIGS. 10( c ) and 10 ( d ) and ⁇ 600% in FIGS. 10( e ) and 10 ( f ), were varied accordingly.
  • Scanning electron microscope micrographs, taken from a porous Ti sintered structure provided by Stryker-Howmedica are shown for reference in FIG. 11 .
  • the Ti on Ti substrate was sectioned, hot mounted and polished using a process of 1200 and 2500 grade SiC, 6 ⁇ m diamond paste and 70/30 mixture of OPS and 30% H 2 O 2 .
  • the polished sample was then etched with 100 ml H 2 O, 5 ml NH.FHF and 2 cm 3 HCl for 30 seconds to bring out the microstructure. Optical images of this sample in section are shown in FIG. 12 .
  • FIG. 13 is an image taken from a non-contact surface profilimentry to show the surface structures obtained when using Ti, CoCr, Ta and Nb on Ti substrates. Values for Ra, Rq and Rb roughness are also shown.
  • the key laser parameters varied for forming the three-dimensional metallic porous structures are: (a) Laser scanning speed (v.) in (mms ⁇ 1 ), which controls the rate at which the laser traverses the powder bed; (b) Laser power, P(W), which in conjunction with the laser spot size controls the intensity of the laser beam. The spot size was kept constant throughout the experiment; (c) Frequency, (Hz) or pulse repetition rate. This variable controls the number of laser pulses per second. A lower frequency delivers a higher peak power and vice versa.
  • the line width can be related to the laser scanning speed and the laser power to provide a measure of specific density, known as the “Andrew Number”, where:
  • the Andrew number is the basis for the calculation of the present invention.
  • the Andrew number may also be calculated by substituting the line separation (d) for beam width (b).
  • the two methods of calculating the Andrew number will result in different values being obtained.
  • line separation (d) as a factor only on track of fused powder is considered, whereas when using the beam width (b) as a factor, two tracks of fused powder are considered as well as the relative influence of one track to the next. For this reason we have chosen to concern our with the Andrew number using scan spacing as a calculating factor. It can thus be appreciated, that the closer these tracks are together the greater the influence they have on one another.
  • the laser power may be varied between 5 W and 1000 W. Utilizing lower power may be necessary for small and intricate parts but would be economically inefficient for such coatings and structures described herein. It should be noted that the upper limit of laser power is restricted because of the availability of current laser technology. However, if a laser was produced having a power in excess of 1000 W, the scanning speed of the laser could be increased in order that an acceptable Andrew number is achieved. A spot size having a range between 5 um(fix) to 500 um(fix) is also possible. For the spot size to increase while still maintaining an acceptable Andrew number, either the laser power must be increased or the scanning speed decreased.
  • the above formula gives an indication of how the physical parameters can vary the quantity of energy absorbed by the powder bed. That is, if the melted powder has limited cohesion, e.g. insufficient melting, the parameters can be varied to concentrate the energy supply to the powder.
  • High Andrew numbers result in reduced pore coverage and an increase in pore size due to the effects of increased melt volume and flow.
  • Low Andrew numbers result in low melt volume, high pore density and small pores.
  • Current satisfactory Andrew numbers are approximately 0.3 J/mm ⁇ 2 to 8 J/mm ⁇ 2 and are applicable to many alternative laser sources. It is possible to use a higher powered laser with increased scanning speed and obtain an Andrew number within the working range stated above.
  • FIGS. 4( a ) to 4 ( c ) are scanning election microscope images of the surface structure of CoCr on stainless steel produced with a laser power of 82 W cw.
  • FIG. 4( a ) was produced with a laser scanning speed of 105 mms ⁇ 1
  • FIG. 4( b ) was produced with a laser scanning speed of 135 mms ⁇ 1 .
  • FIG. 4( a ) was produced with a laser scanning speed of 105 mms ⁇ 1
  • FIG. 4( b ) was produced with a laser scanning speed of 135 mms ⁇ 1 .
  • FIG. 4( c ) is an image of the same structure in FIG. 4( b ), in section. There is a significant self-ordering within the overall structure. Larger columnar structures are selectively built leaving large regions of unmelted powder. It is worth noting that these pillars are around 300 ⁇ m wide, over 1.6 mm tall and fuse well with the substrate, as seen in FIG. 4( c ). Further analysis shows that the use of a hatched scanning format allows porosity to be more sufficiently controlled to allow the pore size to be directly controlled by the beam overlap.
  • Increased fusion may, if required, be obtained by heating the substrate, powder or both prior to scanning.
  • Such heating sources are commonly included in standard selective laser sintering/melting machines to permit this operation.
  • FIG. 26 shows the metallography of the structures with energy dispersive spectroscopy (EDS) revealing the relative metal positions within the build.
  • EDS energy dispersive spectroscopy
  • a typical waffle build of titanium on a titanium substrate was constructed as a way of regulating the porous structure. Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45°45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction to give a structure of adequate strength. Typical parameters employed were: Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of ⁇ 700%. FIG. 27 gives an indication of the effect of line spacing and pore size. FIG.
  • FIG. 28(a) shows typical examples of the waffle structure.
  • the magnification level changes from 10, 20, 30, 70 and 150 times normal viewing as one moves respectively from Fig. (b) to (f).
  • FIG. 28(a) more specifically shows Ti powder on a Ti substrate with a controlled porosity by varying line spacing, i.e., beam overlap.
  • Trabecular structures of titanium on a titanium substrate were constructed as a way of randomising the porous structures.
  • An STL (sterolithography) file representing trabecular structure was produced from a micro CT scan of trabecular bone. This file was sliced and the slice data sent digitally to the scanning control. This allowed the layer-by-layer building of a metallic facsimile to be realised.
  • FIG. 29 shows a cross-sectional view of such a construct.
  • a method for making lattice-type constructs was referred to in the relevant art.
  • a typical example of this type of structure is shown in FIG. 30 .
  • the scanning strategy employed to form such a construct was mentioned and such a strategy could be produced within the range of Andrew numbers outlined.
  • Table 4 shows an indication of scanning strategies and their relationships to the Andrew number.
  • the second and preferred approach uses a continuous scanning strategy whereby the pores are developed by the planar deposition of laser melted powder tracks superimposed over each other. This superimposition combined with the melt flow produces random and pseudorandom porous structures.
  • the properties of the final structure, randomness, interconnectivity, mechanical strength and thermal response are controlled by the process parameters employed.
  • One set of scanning parameters used was: Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45° 45°, 135°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction. The array of sequences was repeated many times to give a construct of the desired height.
  • Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of ⁇ 700%.
  • FIG. 32 shows such a construct.
  • Laser cleaning or acid etching technique may be effective. Additionally, a rigorous cleaning protocol to remove all loose powder may entail blowing the porous structure with clean dry compressed gas, followed by a period of ultrasonic agitation in a treatment fluid. Once dried, a laser scan may be used to seal any remaining loose particles.
  • a typical example of the use of a bond coat is provided by the combination of titanium on to a cobalt chromium substrate. Tantalum also was an effective bond coat in this example. Note that the bond coat may be applied by laser technology, but other methods are also possible such as gas plasma deposition.
  • FIGS. 13( a ) to 13 ( d ) show the surface profile.
  • the Surface Data shown in FIGS. 14( a ) and 14 ( b ) and 15 ( a ) and 15 ( b ) show a coded profile of the plan views of the samples.
  • FIGS. 16 to 25 are scanning electron microscope (SEM) micrographs of a series of single layer Ti on CoCr and Ti on Ti images that were produced prior to the multi-layer builds shown in FIGS. 8 and 9 respectively and as follows.
  • the method according to the present invention can produce surface structures on all powder/baseplate combinations with careful selection of process parameters.
  • the process is carried out on flat baseplates that provide for easy powder delivery in successive layers of around 100 ⁇ m thickness. Control of powder layer thickness is very important if consistent surface properties are required.
  • the application of this technology can also be applied to curved surfaces such as those found in modern prosthetic devices; with refinements being made to the powder layer technique.
  • the structures have all received ultrasonic and aqueous cleaning.
  • the resultant porous surfaces produced by the Direct Laser Remelting process exhibit small particulates that are scattered throughout the structure. It is unclear at this stage whether these particulates are bonded to the surface or loosely attached but there are means to remove the particulates if required.
  • the Direct Laser Remelting process has the ability to produce porous structures that are suitable for bone in-growth applications.
  • the powdered surfaces have undergone considerable thermal cycling culminating in rapid cooling rates that have produced very fine dendritic structures (e.g. FIGS. 13( a ) to 13 ( d )).
  • the Direct Laser Remelting process can produce effective bone in-growth surfaces and the manufacturing costs are reasonable.
  • the object has been to provide a porous structure on a base but the present invention can also be used to provide a non-porous structure on such a base to form a three-dimensional structure.
  • the same techniques can be utilized for the materials concerned but the laser processing parameters can be appropriately selected so that a substantially solid non-porous structure is achieved.
  • a technique can be used to deposit the powder onto a suitable carrier, for example a mold, and to carry out the process without the use of a base so that a three-dimensional structure is achieved which can be either porous, as described above, or non-porous if required.
  • this method can, therefore, be used to produce article from the metals referred to which can be created to a desired shape and which may or may not require subsequent machining. Yet again, such an article can be produced so that it has a graded porosity of, e.g., non-porous through various degrees of porosity to the outer surface layer.
  • Such articles could be surgical prostheses, parts or any other article to which this method of production would be advantageous.

Abstract

A method of fabricating a porous or partially porous three-dimensional metal article for use as a tissue ingrowth surface on a prosthesis. The porous article is formed using direct laser remelting in a cross section of a layer of metallic powder on a build platform without fusing thereto. The power, speed, spot size and beam overlap of the scanning laser is coordinated so that a predetermined porosity of the metallic powder can be achieved. Laser factors also vary depending from the thickness of the powder layer, type of metallic powder and size and size distribution of the powder particles. Successive depositing and remelting of individual layers are repeated until the article is fully formed by a layer-by-layer fashion. In an additional embodiment, a first layer of metallic powder may be deposited on a solid base or core and fused thereto.

Description

    CROSS REFERENCE TO RELATED APPLICATIONS
  • This application is a continuation of U.S. application Ser. No. 10/704,270, filed on Nov. 7, 2003, which claims the benefit of U.S. Provisional Application No. 60/424,923 filed on Nov. 8, 2002, and U.S. Provisional Application No. 60/425,657 filed on Nov. 12, 2002, the disclosures of which are incorporated herein by reference.
  • BACKGROUND OF THE INVENTION
  • The present invention relates to a porous surface and a method for forming the same, which uses a directed energy beam to selectively remelt a powder to produce a part. In particular, this invention relates to a computer-aided laser apparatus, which sequentially remelts a plurality of powder layers to build the designed part in a layer-by-layer fashion. The present application is particularly directed toward a method of forming a porous and partially porous metallic structure.
  • DESCRIPTION OF THE RELEVANT ART
  • The field of free-form fabrication has seen many important recent advances in the fabrication of articles directly from computer controlled databases. These advances, many of which are in the field of rapid prototyping of articles such as prototype parts and mold dies, have greatly reduced the time and expense required to fabricate articles, particularly in contrast to conventional machining processes in which a block of material, such as a metal, is machined according to engineering drawings.
  • One example of a modern rapid prototyping technology is the selective laser sintering process practiced by systems available from DTM Corporation of Austin, Tex. According to this technology, articles are produced in layer-wise fashion from a laser-fusible powder that is dispensed one layer at a time. The powder is fused, remelted or sintered, by the application of laser energy that is directed in raster-scan fashion to portions of the powder layer corresponding to a cross section of the article. After the fusing of the powder in each layer, an additional layer of powder is dispensed, and the process repeated, with fused portions or lateral layers fusing so as to fuse portions of previous laid layers until the article is complete. Detailed descriptions of the selective laser sintering technology may be found in U.S. Pat. No. 4,863,538, U.S. Pat. No. 5,017,753, U.S. Pat. No. 5,076,869 and U.S. Pat. No. 4,944,817, all assigned to Board of Regents, the University of Texas. Quasi-porous structures have also been developed in the form of regular and irregular lattice arrangements in which individual elements (column and connecting cross-members) are constructed singularly from a pre-defined computer-aided design model of the external geometry and lattice structure. The selective laser remelting and sintering technologies have enabled the direct manufacture of solid or dense three-dimensional articles of high resolution and dimensional accuracy from a variety of materials including wax, metal powders with binders, polycarbonate, nylon, other plastics and composite materials, such as polymer-coated metals and ceramics.
  • The field of the rapid prototyping of parts has, in recent years, made large improvements in broadening high strain, high density, parts for use in the design and pilot production of many useful articles, including metal parts. These advances have permitted the selective laser remelting and sintering processes to now also be used in fabricating prototype tooling for injection molding, with expected tool life in access of ten thousand mold cycles. The technologies have also been applied to the direct fabrication of articles, such as molds, from metal powders without a binder. Examples of metal powder reportedly used in such direct fabrication include two-phase metal powders of the copper-tins, copper-solder (the solder being 70% led and 30% tin), and bronze-nickel systems. The metal articles formed in these ways have been quite dense, for example, having densities of up to 70% to 80% of fully dense (prior to any infiltration). Prior applications of this technology have strived to increase the density of the metal structures formed by the remelting or sintering processes. The field of rapid prototyping of parts has focused on providing high strength, high density, parts for use and design in production of many useful articles, including metal parts.
  • However, while the field of rapid prototyping has focused on increasing density of such three-dimensional structures, the field has not focused its attention on reducing the density of three-dimensional structures. Consequently, applications where porous and partially porous metallic structures, and more particularly metal porous structures with interconnected porosity, are advantageous for use have been ignored. It is an object of this invention to use a laser and powder metal to form pores in structures in which pores are irregular in size and have a controlled total porosity. It is a further object to produce porous tissue in growth surfaces with interconnected porosity with uniform pores and porosity.
  • BRIEF SUMMARY OF THE INVENTION
  • The present invention relates to a method for producing a three-dimensional porous structure particularly for use with tissue ingrowth. In one embodiment of the present invention, a layer of metallic powder is deposited onto a substrate or a build platform. Preferred metals for the powder include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. A laser beam with predetermined settings scans the powder layer causing the powder to preferentially remelt and consequently solidify with a decreased density, resulting from an increase in porosity as compared to a solid metal. The range of the laser's power may be between 5 W and 1000 W. After the first layer of powder has been completed, successive offset layering and remelting are continued until the porous part has been successfully completed. In this embodiment, the benefit of the part formed is that that decreased density increases porosity thus enabling the part to be used for, among other things, tissue ingrowth.
  • In a second embodiment, the first layer of metallic powder is deposited onto a solid base or core and fused thereto. Preferred metals used for the core include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium. Successive powder layers of the same or different materials are once again added in a layer-by-layer fashion until the part is completed. This embodiment has the desired effect of providing a structure in which the porosity may be increased as the structure is built, resulting in a graded profile in which the mechanical properties will also be reduced outwards from the core. This will allow the formed part to be used for, among other things, medical implants and prosthesis, but yet still include a surface for tissue ingrowth.
  • The method of producing a three-dimensional porous tissue ingrowth structure may include depositing a first layer of a powder made from a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, onto a substrate. Followed by scanning a laser beam at least once over the first layer of powder. The laser beam having a power (P) in Joule per seconds with a scanning speed (v) in millimeters per second with a range between 80 and 400 mms. and a beam overlap (b) in millimeters of between 50% and −1200%. Such that the number calculated by the formula P/(b×v) lies between the range 0.3-8 J/mm2.
  • At least one additional layer of powder is deposited and then the laser scanning steps for each successive layer are repeated until a desired web height is reached. In a second embodiment, during the step of repeating the laser scanning steps, at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
  • The thickness of the first layer and said successive layers of powder is between 5 μm-2000 μm. The laser can be applied either continuously or in a pulse manner, with the frequency of the pulse being in the range of approximately 1 KHz to 50 KHz. Preferably, the method is carried out under an inert atmosphere, more preferably specifically an Argon inert atmosphere.
  • In order to achieve a greater mechanical strength between the base or core and the first layer of powder a third metal may be used to act as an intermediate. The third metal would act as a bond coat between the core and first layer of powder. Additionally the core may be integral with the resultant porous ingrowth structure and impart additional physical properties to the overall construct. The core may also be detachable from the resultant porous surface buildup.
  • It is the object of the present invention to provide a method of fabricating porous and partially porous metallic structures with a known porosity for use in particularly but not exclusively hard or soft tissue interlock structures or medical prosthesis.
  • These and other objects are accomplished by a process of fabricating an article in which laser-directed techniques are used to produce a porous three-dimensional structure with interconnected porosity and predetermined pore density, pore size and pore-size distribution. The article is fabricated, in the example of remelting, by using a laser and varying either the power of the laser, the layer thickness of the powder, laser beam diameter, scanning speed of the laser or overlap of the beam. In fabricating a three-dimensional structure, the powder can be either applied to a solid base or not. The article is formed in layer-wise fashion until completion.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • Methods of forming the porous surface of the present invention can be performed in many ways and some embodiments will now be described by way of example and with reference to the accompanying drawings in which:
  • FIG. 1 is a diagrammatic illustration of the apparatus used to make test samples according to the processes of the present invention;
  • FIG. 2 is a photographic image showing an array of samples produced by the processes as performed by the apparatus of FIG. 1;
  • FIG. 3 is a table showing a series of parameters used for the samples of FIG. 2;
  • FIGS. 4 to 10 are scanning electron microscope images of the surface structure of various samples made by the method according to the invention;
  • FIG. 11 is a scanning electron microscope micrograph taken from a porous Ti sintered structure;
  • FIG. 12 is an optical image of a section through a sample showing the microstructure;
  • FIG. 13 is an image detailing surface structures;
  • FIGS. 14 and 15 are non-contact surface profilimetry images detailing plan views of the samples; and
  • FIGS. 16 to 25 are scanning electron microscope micrographs produced prior to multi-layer builds shown in FIGS. 7 and 8.
  • FIG. 26 indicates the metallography and spectra of a typical bond coat structure.
  • FIG. 27 shows the effect of line spacing on pore size.
  • FIG. 28 a-f are examples of typical waffle structures.
  • FIG. 29 is a trabecular bone-type structure constructed from a micro CT scan.
  • FIG. 30 shows typical freestanding structures.
  • FIG. 31 shows a freestanding structure built using the preferred scanning strategy.
  • DETAILED DESCRIPTION
  • The present invention relates to a method of forming porous and partially porous metallic structures which are particularly but not exclusively applicable for use in hard or soft tissue interlock structures for medical implants and prosthesis. The method makes use of laser technology by employing a variety of scanning strategies. Typical metal and metal alloys employed include stainless steel, cobalt chromium alloys, titanium and its alloys, tantalum and niobium, all of which have been used in medical device applications. The present invention can be used for such medical device applications where bone and soft tissue interlock with a component is required, or where a controlled structure is required to more closely match the mechanical properties of the device with surrounding tissue. Additionally, the present invention may be employed to enhance the biocompatibility of a porous structure with animal tissue. With these advantages in mind, a structure may be created using specific dimensions required to accommodate a particular patient.
  • One particular intention of the present invention is to produce a three-dimensional structure using a direct laser remelt process, for example, for building structures with or without a solid base or core. When applied to an orthopedic prosthesis, the three-dimensional structure could be used to provide a porous outer layer to form a bone in-growth structure. Alternatively, the porous structure, when applied to a core, could be used to form a prosthesis with a defined stiffness to both fulfill the requirement of a modulus match with surrounding tissue and provide interconnected porosity for tissue interlock. A further use could be to form an all-porous structure with grade pore size to interact with more than one type of tissue. Again, the process can be used to build on a solid base or core with an outer porous surface, the porosity of which is constant or which varies. The base or core materials to which the process is applied is either titanium and its alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. The preferred surface coatings are titanium, cobalt chrome and tantalum but both stainless steel and niobium can also be used. Fully porous structures may be built from any of the materials tested, with the preferred material being titanium. One intention of the present invention is to produce a method which can be exploited on a commercial basis for the production of, for example, bone interlock surfaces on a device although it has many other uses.
  • According to the present invention, a method of forming a three-dimensional structure includes building the shape by laser melting powdered titanium and titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. The laser may be a continuous wave or pulsed laser beam.
  • The method can be performed so that the structure is porous and if desired, the pores can be interconnecting to provide an interconnected porosity.
  • If desired, the method can include using a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum, on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam. Thus, a mixture of desired mixed materials may be employed.
  • Thus, the method can be applied to an existing article made from cobalt chrome, titanium or titanium alloys, stainless steel, tantalum or niobium, such as an orthopedic implant, to produce a porous outer layer from any of the aforementioned metals or alloys to provide a bone in-growth structure.
  • Preferably, prior to the deposition of any powder onto a substrate, a cleaning operation to ensure a contaminant-free surface may be employed. Typically, this process may include a solvent wash followed by a cleaning scan of the laser beam without the presence of particles.
  • In order to increase the mechanical bond between a substrate i.e., core or base, and a first layer of deposited powder a coating process may be employed. The coating process includes applying a third metal directly to the substrate, which has a higher bond strength to the substrate then does the first layer of powder. This process is particularly useful when the substrate and first powder layer are of different materials. The process of coating the substrate may be accomplished using known processes including laser deposition, plasma coating, cold gas dynamic spraying or similar techniques. One example of the coating process includes using either niobium or tantalum as an interface between a cobalt chrome alloy substrate and a first layer of titanium powder.
  • The present invention can also include a laser melting process, which precludes the requirement for subsequent heat treatment of the structure, thereby preserving the initial mechanical properties of the core or base metal.
  • The present invention may be applied to produce an all-porous structure using any of the aforementioned metal or metal alloys. Such structures can be used as finished product or further processed to form a useful device for either bone or soft tissue in-growth. Additionally, the structure may be used to serve some other function such as that of a lattice to carry cells.
  • The pore density, pore size and pore size distribution can be controlled from one location on the structure to another. It is important to note that successive powder layers can differ in porosity by varying factors used for laser scanning powder layers. As for example, a first layer of powder is placed and subsequently scanned. Next a second layer of powder is placed and scanned. In order to control porosity the second scan may be angled relative to the first scan. Additionally, the angling of the scanning as compared to previous and post scans may be maneuvered and changed many times during the process of building a porous structure. If a structure was built without alternating the angling of any subsequent scans you would produce a structure having a plurality of walls rather than one with an interconnecting or non-interconnecting porosity.
  • In one such method, the laser melting process includes scanning the laser beam onto the powder in parallel scan lines with a beam overlap i.e., scan spacing, followed by similar additional scans or subsequent scans at 90°. The type of scan chosen may depend on the initial layer thickness as well as the web height required. Web height refers to the height of a single stage of the porous structure. The web height may be increased by deposited additional layers of powder of a structure and scanning the laser at the same angle of the previous scan.
  • Further, the additional scan lines may be at any angle to the first scan, to form a structure with the formation of a defined porosity, which may be regular or random. The scan device may be programmed to proceed in a random generated manner to produce an irregular porous construct but with a defined level of porosity. Furthermore, the scan can be pre-programmed using digitized images of various structures, such as a trabecular bone, to produce a similar structure. Contrastingly, the scan may be pre-programmed using the inverse of digitized images, such as the inverse of a digitized trabecular bone to produce trabecular shaped voids. Many other scanning strategies are possible, such as a waffle scan, all of which can have interconnecting porosity if required.
  • The beam overlap or layer overlap may be achieved by rotation of the laser beam, the part being produced, or a combination of both.
  • A first method according to the present invention is intended to produce a porous structure for bone in-growth on the outer surface layer of a prosthesis.
  • To produce a porous surface structure, the nature of the material formed as a result of laser melting of powdered beads is principally dependent on the thermal profile involved (heating rate, soaking time, cooling rate); the condition of the raw material (size and size distribution of powder particles); atmospheric conditions (reducing, inert or oxidizing chamber gas); and accurate control of the deposited layer thickness.
  • There have been a number of studies to determine the optimum pore structure for maximization of bone in-growth on prostheses. The general findings suggest that optimum porosity is between approximately 20% and 40%, and aim to mid value with a mean volume percent of voids of about 70%. The preferred pore structure is irregular and interconnected, with a minimum pore size between about 80 μm and 100 μm and a maximum pore size between 80 μm and 800 μm. The structured thickness for in-growth is 1.4-1.6 mm, but can be larger or smaller depending on the application. As for example, it may be necessary to produce even smaller pore sizes for other types of tissue interaction or specific cellular interaction.
  • The first phase of development of the present invention involved an investigation, designed to characterize the material transformation process and to identify the optimum parameters for processing using three substrate materials CoCr and Ti stainless steel alloys, with five powder types Ti, CoCr, Ta and Nb, stainless steel.
  • The initial Direct Laser Remelting trials explored a comprehensive range of process parameters during the production of a number of coated base substrates. Results from this task were evaluated using laser scanning and white light interferometry in order to define the range of process parameters that produced the optimum pore structure.
  • Referring to FIG. 1, there is shown the apparatus used to carry out the method which comprises an Nd; YAG industrial laser 10 manufactured by Rofin Sinar Lasers, in Hamburg, Germany, integrated to an RSG1014 analogue galvo-scanning head 12 providing a maximum scan speed of 500 mm/s. The laser beam 14 is directed into an atmospherically controlled chamber 16, which consists of two computer-controlled platforms for powder delivery and part building. The powder is delivered from a variable capacity chamber 18 into the chamber 16 and is transported by a roller 20 to a build platform 22 above a variable capacity build chamber 24. In the embodiment shown in FIG. 1, the build and delivery system parameters are optimized for an even 100 μm coating of powder to be deposited for every build layer. The metals chosen as surface materials are all difficult to process due to their affinity for oxygen. Cr and Ti are easily oxidized when processed by laser in oxygen-containing atmosphere, their oxide products have high melting points and poor flowability. For this reason, and to prevent the formation of other undesirable phases, the methods were carried out under an Argon inert atmosphere in chamber 16. Pressure remained at or below atmospheric pressure during the entire application.
  • The build chamber 24 illustrated in FIG. 1 and method of layering described above is suitable for test specimens and constructs such as three-dimensional freestanding structures. However, in order to build on to an existing device, such as acetabular metal shells, hip and knee femoral components, knee tibial components and other such devices, considerable changes to the powder laying technique would need to be applied.
  • Preliminary experiments were performed on CoCr alloy to determine the efficacy of in-situ laser cleaning of the substrate. Typical processing conditions were: Laser power of 82 W, pulse frequency of 30 KHz, and a laser scan speed of 160 mm/sec.
  • Preliminary experiments were performed on CoCr to assess the environment conditions within the chamber. In these examples, Co212-e Cobalt Chrome alloy was used. The CoCr was configured into square structures, called coupons. Arrays of CoCr coupons were built onto a stainless steel substrate. The Co212-e Cobalt Chrome alloy had a particle size distribution of 90<22 um, i.e., 90% of the particles are less than 22 μm, the composition of which is shown in the table below.
  • TABLE 1
    Composition of Co212-e CoCr alloy
    Element
    Cr Mo Si Fe Mn Ni N C Co
    Wt % 27.1 5.9 0.84 0.55 0.21 0.20 0.16 0.050 Balance
  • An array of nine sample coupons were produced as shown in FIG. 2, with the process of Table 2, using a maximum laser power of 78 watts (W) and laser scanning speed for each coupon varying between 100-260 mms−1. Of course a higher laser power may be employed; however, a higher laser power would also necessitate increasing the speed of the laser scan speed in order to produce the desired melting of the powder layer. A simple linear x-direction scan was used on each of the coupons. This allowed the processing parameter, beam overlap, to be used to control the space between successive scan lines. That is, with a 100 μm laser spot size, an overlap of −200% produces a 100 μm gap between scans. Although the acceptable range for the beam overlap is given at +50% to −1200% it should be duly noted that the negative number only refers to the fact the there is a gap as opposed to a beam overlap between successive scans. For instance a beam overlap of zero refers to the fact that successive scans on the same layer of powder border each other. If the beam overlap was 5% then 5% of the first scan is overlapped by the second scan. When computing the Andrew number the absolute value of the beam overlap is used. The complete set of process parameters used is shown in Table 2 below.
  • TABLE 2
    Process parameters
    Power Layer Beam Scanning Overlap
    Watts Thickness Diameter Speed No. of (% of line
    (W) (μm) (μm) (mms−1) Atmosphere Layers width)
    78 100 100 100-260 No 16 25, 50, −500
  • The incremental changes in scanning speed and the size of the speed range were modified as the experiments progressed. To begin with, a large range of speeds was used to provide an initial indication of the material's performance and the propensity to melt. As the experiments progressed, the range was reduced to more closely define the process window. Speed and beam overlap variations were used to modify the specific energy density being applied to the powder bed and change the characteristics of the final structure. The complete series of parameters are given in FIG. 3, the parameters sets used for the definitive samples are shaded in gray.
  • CoCr was the first of four powders to be examined and, therefore, a wide range of process parameters was used. In each case, laser power and the pulse repetition rate were kept constant, i.e., continuous laser pulse, to allow the two remaining parameters to be compared. Layer thickness was maintained at 100 μm throughout all the experiments described here. Layer thickness can, however, vary between 5 μm to 2000 μm.
  • On completion of the initial series of experiments using CoCr powder on 2.5 mm thick stainless steel substrates, basic optical analysis was conducted of the surface of the coupons to ascertain the size of the pores and degree of porosity being obtained. Once a desired pore size was obtained and the coupons had suitable cohesion, the two experiments closest to the optimum desired pore size were repeated using first CoCr and then Ti substrates. The same structure could be obtained by other parameters.
  • Following the conclusion of the CoCr experiments, the remaining three powders; Niobium, Tantalum and Titanium were investigated in turn. The procedure followed a simple course although fewer parameter sets were explored as the higher melting points of these materials forced the reduction in speeds compared to CoCr powder.
  • For Niobium, the particle size description was 80%<75 μm at a purity of 99.85%. Due to its higher melting temperature compared to that of CoCr (Nb being at about 2468° C., and CoCr being at about 1383° C.), the laser parameters used included a reduced scanning speed range and increased beam overlap providing increased specific energy density at the powder bed. In addition, the pulse repetition rate was varied from 20 kHz to 50 kHz.
  • On completion of a small number (four in total) of preliminary experiments of Nb on stainless steel substrate, the experiment with the most ideal parameters was repeated on both the CoCr and Ti substrates.
  • The Tantalum used in this study had a particular size distribution of 80%<75 μm with a purity of 99.85%. Ta has a melting point of about 2996° C. and was processed using the same laser parameters as Nb. Now confident of the atmospheric inertness, the Ta powder was melted directly onto the CoCr and Ti substrates.
  • Bio-medical alloys of Titanium were not readily available in powder form and so pure Ti was chosen. The particle size distribution for the Ti powder was 80%<45 μm with a purity of 99.58%. The same parameters used for Nb and Ta were also used for the Ti powder. Ti has a lower melting point than Ta or Nb, Ti being at about 1660° C., but has a higher thermal conductivity than Ta or Nb. This implies that although the powder should require less energy before melting, the improved heat transfer means a larger portion of the energy is conducted away from the melt pool.
  • Following the completion of samples with all four powders on the required substrates, surface analysis was conducted using optical analysis and a scanning electron microscope to obtain images of the resultant pores. Porosity was calculated using a simple image processing technique involving the setting of contrast thresholds and pixel counting. While this technique is not the most accurate method, it allows the rapid analysis of small samples produced. Techniques such as Xylene impregnation would yield more accurate results but they are time consuming and require larger samples than those produced here.
  • Following an extended series of experimentation, two sets of laser processing parameters were selected for the laser melting of CoCr powder. From analysis of the stainless steel substrates, it was seen that a large portion of the results fell within the pore size required for these materials, stated as being in the range of 80 μm to 400 μm.
  • Optical analysis of the surface structure of each of the coupons produced with CoCr on CoCr and Ti alloy substrates were initially viewed but due to problems with the depth of field associated with an optical microscope, little information could be extracted. In addition to the coupons that were produced to satisfy the project requirements, two experiments were conducted using a relatively large negative beam overlap of −250 and −500%. Optical images of the coupon's surface and in section are shown in FIG. 4. These were not the definitive parameters chosen for the final arrays on CoCr and Ti alloy substrates as the pore size exceeds the required 80 μm to 400 μm. They are shown here to display what the Direct Laser Remelting process can produce when an excessive beam overlap is used.
  • To provide a clearer indication of the pore size and pore density, the optical analysis was repeated using images obtained from the scanning electron microscope. FIG. 5 is an image of two coupons produced from a CoCr array on Ti alloy substrates. This array was chosen because it best satisfied the requirements of this exercise. The parameters were: laser power of 82 W continuous wave (cw); 25% beam overlap; scanning speed varied from 100 mms−1 to 260 mms−1 in 20 mm−1 increments; the images of the coupons shown here, taken from this array, were produced with scanning speeds of 180 mms−1 to 200 mms−1. The surface is comprised of fused pathways that develop a network of interconnected pores. This structure continues throughout the layer until the interface is reached. The interface is characterized by a patchwork of fusion bonds. These bond sites are responsible for securing the interconnected surface structure to the baseplate. The macroscopic structure is covered with unmelted powder particles that appear to be loosely attached. In addition, there are larger resolidified globules that may have limited bonding to the surface.
  • FIGS. 6 and 7 are the scanning electron microscope images produced from the Nb and Ta coupons on Ti alloy substrates. Specifically, FIGS. 6( a) to 6(e) are scanning election microscope images of the surface structure of Nb on Ti alloy substrates, produced with a laser power of 82 W cw, −40% beam overlap. The scanning speeds used were: 160 mms−1 for FIG. 6( a), 190 mms−1 for FIG. 6( b), 200 mms−1 for FIG. 6( c), 210 mms−1 for FIG. 6( d) and 240 mms−1 for FIG. 6( e), respectively.
  • FIGS. 7( a) to 7(c) are scanning election microscope images of the surface structure of Ta on Ti alloy substrates produced using the same parameters used in the Nb or Ti alloy substrates except: FIG. 7( a) was produced with a scanning speed of 160 mms−1; FIG. 7( b)'s speed was 200 mms−1 and FIG. 7( c)'s speed was 240 mms−1, respectively. An increased beam overlap was used here as Nb and Ta have high melting points, which require a greater energy density. The surfaces once again exhibit significant levels of unmelted powder particles and loosely attached resolidified beads that vary in size from a few microns to several hundred microns. All samples were loosely brushed after completion and cleaned in an ultrasonic aqueous bath. It is possible that further cleaning measures may reduce the fraction of loose particles.
  • FIGS. 8( a) to 8(e) are scanning electron microscope images taken from the Ti coupons on the CoCr alloy substrates. The laser processing parameters used were the same as those for the Nb and Ta powders, with once again only the speed varying. The scanning speed was varied from 160 mms−1 (FIG. 8( a), 170 mms−1 (FIG. 8( b)), 200 mms−1 (FIG. 8( c)); 230 mms−1 (FIG. 8( d) to 240 mms−1 (FIG. 8( e)). The Ti coupon on CoCr samples, (FIGS. 8( a) to 8(c)) indicate very high density levels compared to the other examples. The line-scans can be clearly seen, with good fusion between individual tracks, almost creating a complete surface layer. The surface begins to break up as the scanning speed is increased.
  • FIGS. 9( a) to 9(e) are scanning electron microscope images of surface structures of Ti on Ti alloy substrates produced with the same parameters used in FIGS. 8( a) to 8(e), respectively. It is unclear why Ti should wet so well on CoCr substrates. In comparison, Ti on Ti exhibits similar characteristic patterns as with Nb, Ta, and CoCr, specifically, an intricate network of interconnected pores.
  • Following the completion of the multi-layer coupons, a series of 20 mm×20 mm structures were produced from Ti that utilized an X and Y-direction “waffle” scanning format using the optimum Ti operating parameters with the two scans being orthogonal to one another. The intention behind these experiments was to demonstrate the ability of the Direct Laser Remelting process to produce parts with a controlled porosity, e.g. internal channels of dimensions equal to the required pore size, e.g. 80 μm to 400 μm. To do this, a relatively large beam overlap of between −400% and −600% was used. Scanning electron microscope images of the surfaces of these structures are shown in FIGS. 10( a) to 10(f). The scanning speed, 160 mms−1 and the laser power 72 W cw were kept constant while the beam overlaps; −400% in FIGS. 10( a) and 10(b); −500% in FIGS. 10( c) and 10(d) and −600% in FIGS. 10( e) and 10(f), were varied accordingly. Scanning electron microscope micrographs, taken from a porous Ti sintered structure provided by Stryker-Howmedica are shown for reference in FIG. 11.
  • To illustrate more clearly the interaction between the substrate/structure metallurgical interaction, the Ti on Ti substrate was sectioned, hot mounted and polished using a process of 1200 and 2500 grade SiC, 6 μm diamond paste and 70/30 mixture of OPS and 30% H2O2. The polished sample was then etched with 100 ml H2O, 5 ml NH.FHF and 2 cm3 HCl for 30 seconds to bring out the microstructure. Optical images of this sample in section are shown in FIG. 12.
  • FIG. 13 is an image taken from a non-contact surface profilimentry to show the surface structures obtained when using Ti, CoCr, Ta and Nb on Ti substrates. Values for Ra, Rq and Rb roughness are also shown.
  • From the optical and scanning election microscope analysis conducted, it is apparent that the Direct Laser Remelting process is capable of satisfying the requirements for pore characteristics, concerning maximum and minimum pore size, interconnectivity and pore density. From the initial visual analysis of the CoCr coupons, it was apparent from these and other examples, that subtle variations in pore structure and coverage could be controlled by scanning velocity and line spacing.
  • The key laser parameters varied for forming the three-dimensional metallic porous structures are: (a) Laser scanning speed (v.) in (mms−1), which controls the rate at which the laser traverses the powder bed; (b) Laser power, P(W), which in conjunction with the laser spot size controls the intensity of the laser beam. The spot size was kept constant throughout the experiment; (c) Frequency, (Hz) or pulse repetition rate. This variable controls the number of laser pulses per second. A lower frequency delivers a higher peak power and vice versa.
  • The line width can be related to the laser scanning speed and the laser power to provide a measure of specific density, known as the “Andrew Number”, where:
  • An = P b × v ( J / mm - 2 )
  • Where P denotes the power of the laser, v is the laser scanning speed and b denotes beam width of the laser. The Andrew number is the basis for the calculation of the present invention. The Andrew number may also be calculated by substituting the line separation (d) for beam width (b). The two methods of calculating the Andrew number will result in different values being obtained. When using line separation (d) as a factor only on track of fused powder is considered, whereas when using the beam width (b) as a factor, two tracks of fused powder are considered as well as the relative influence of one track to the next. For this reason we have chosen to concern ourselves with the Andrew number using scan spacing as a calculating factor. It can thus be appreciated, that the closer these tracks are together the greater the influence they have on one another.
  • Additionally, the laser power may be varied between 5 W and 1000 W. Utilizing lower power may be necessary for small and intricate parts but would be economically inefficient for such coatings and structures described herein. It should be noted that the upper limit of laser power is restricted because of the availability of current laser technology. However, if a laser was produced having a power in excess of 1000 W, the scanning speed of the laser could be increased in order that an acceptable Andrew number is achieved. A spot size having a range between 5 um(fix) to 500 um(fix) is also possible. For the spot size to increase while still maintaining an acceptable Andrew number, either the laser power must be increased or the scanning speed decreased.
  • The above formula gives an indication of how the physical parameters can vary the quantity of energy absorbed by the powder bed. That is, if the melted powder has limited cohesion, e.g. insufficient melting, the parameters can be varied to concentrate the energy supply to the powder. High Andrew numbers result in reduced pore coverage and an increase in pore size due to the effects of increased melt volume and flow. Low Andrew numbers result in low melt volume, high pore density and small pores. Current satisfactory Andrew numbers are approximately 0.3 J/mm−2 to 8 J/mm−2 and are applicable to many alternative laser sources. It is possible to use a higher powered laser with increased scanning speed and obtain an Andrew number within the working range stated above.
  • Line spacing or beam overlap can also be varied to allow for a gap between successive scan lines. It is, therefore, possible to heat selected areas. This gap would allow for a smaller or larger pore size to result. The best illustration of this is shown in FIGS. 4( a) to 4(c) where a −500% beam overlap has been applied. FIGS. 4( a) to 4(c) are scanning election microscope images of the surface structure of CoCr on stainless steel produced with a laser power of 82 W cw. FIG. 4( a) was produced with a laser scanning speed of 105 mms−1 and FIG. 4( b) was produced with a laser scanning speed of 135 mms−1. FIG. 4( c) is an image of the same structure in FIG. 4( b), in section. There is a significant self-ordering within the overall structure. Larger columnar structures are selectively built leaving large regions of unmelted powder. It is worth noting that these pillars are around 300 μm wide, over 1.6 mm tall and fuse well with the substrate, as seen in FIG. 4( c). Further analysis shows that the use of a hatched scanning format allows porosity to be more sufficiently controlled to allow the pore size to be directly controlled by the beam overlap.
  • The use of an optical inspection method to determine this approximate porosity is appropriate given the sample size. This method, although not accurate due to the filter selection process, can, if used carefully, provide an indication of porosity. An average porosity level of around 25% was predicted. This porosity level falls within the range of the desired porosity for bone in-growth structures. The mechanical characteristics of the porous structures are determined by the extent of porosity and the interconnecting webs. A balance of these variables is necessary to achieve the mechanical properties required by the intended application.
  • Increased fusion may, if required, be obtained by heating the substrate, powder or both prior to scanning. Such heating sources are commonly included in standard selective laser sintering/melting machines to permit this operation.
  • Following trials on the titanium build on the cobalt chromium substrate, it was determined that the interface strength was insufficient to serve the intended application. Trials were made by providing a bond coat of either tantalum or niobium on the cobalt chromium substrate prior to the deposition of the titanium layers to for the porous build. The typical protocol involved:
      • (i) Initial cleaning scan with a scan speed between 60 to 300 mm/sec, laser power 82 watts, frequency of 30 KHz, and a 50% beam overlap.
      • (ii) Niobium or tantalum deposition with three layers of 50 μm using a laser power of 82 watts, frequency 30 to 40 KHz, with a laser speed of between 160 to 300 mm/sec. The beam overlap was low at 50% to give good coverage.
      • (iii) A build of porous titanium was constructed using a laser power of 82 watts, frequency between 0 (cw) and 40 KHz, scanning speed of between 160 and 240 mm/sec, and beam overlap of −700%.
        The strengths of the constructs are indicated in Table 3 with a comparison of the values obtained without the base coat.
  • TABLE 3
    MAXIMUM TENSILE
    LOAD STRENGTH
    SPECIMEN (kN) (MPa) FAILURE MODE
    Ti on CoCr 2.5 5 Interface
    Ti on CoCr 3.1 6.2 Interface
    1 (Nb on 13.0 26.18 65% adhesive, 35% bond
    Co—Cr) interface
    4 (Ti on Nb 7.76 15.62 Mostly bond coat
    on Co—Cr) interface
    5 (Ti on Nb 9.24 18.53 20% adhesive, 40% bond
    on Co—Cr) coat, 40% porous Ti
    6 (Ti on Ta 11.58 23.33 Mostly adhesive with
    on Co—Cr) discrete webbing
    weakness
    8 (Ta on 13.93 27.92 60% adhesive, 40% bond
    Co—Cr) interface
    9 (Ti on Ta 6.76 13.62 100% bond interface
    on Co—Cr)

    FIG. 26 shows the metallography of the structures with energy dispersive spectroscopy (EDS) revealing the relative metal positions within the build.
  • A typical waffle build of titanium on a titanium substrate was constructed as a way of regulating the porous structure. Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45°45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction to give a structure of adequate strength. Typical parameters employed were: Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of −700%. FIG. 27 gives an indication of the effect of line spacing and pore size. FIG. 28(a) shows typical examples of the waffle structure. The magnification level changes from 10, 20, 30, 70 and 150 times normal viewing as one moves respectively from Fig. (b) to (f). FIG. 28(a) more specifically shows Ti powder on a Ti substrate with a controlled porosity by varying line spacing, i.e., beam overlap.
  • Trabecular structures of titanium on a titanium substrate were constructed as a way of randomising the porous structures. An STL (sterolithography) file representing trabecular structure was produced from a micro CT scan of trabecular bone. This file was sliced and the slice data sent digitally to the scanning control. This allowed the layer-by-layer building of a metallic facsimile to be realised. FIG. 29 shows a cross-sectional view of such a construct.
  • A method for making lattice-type constructs was referred to in the relevant art. A typical example of this type of structure is shown in FIG. 30. The scanning strategy employed to form such a construct was mentioned and such a strategy could be produced within the range of Andrew numbers outlined. Table 4 shows an indication of scanning strategies and their relationships to the Andrew number.
  • TABLE 4
    RELATIVE
    BUILD
    SCAN PARAMETER LAYER PLATFORM
    LAYER STRATEGY SET THICKNESS POSITION ADDITIONAL
    Ti on Ta on CoCr Experimental Procedure.
    Initial Tantalum Coating
    Zero
    0
    Distance
    Between
    Roller &
    Build
    Platform
    0 1st layer 50 μm  −50 μm
    thickness
    set using
    feeler
    gauges but
    powder not
    laid in
    preparation
    for
    cleaning
    scan with
    no powder.
    1 50% Beam P = 82 W Initial
    Overlap Qs = 30 kHz Cleaning
    v = 60 mm/s Scan (no
    An = powder)
    27.333 J/mm2
    Circular P = 82 W Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    2 Circular P = 82 W 50 μm −100 μm Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    3 Circular P = 82 W 50 μm −150 μm Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    Final Titanium Coating
    0 1st layer −150 μm
    thickness
    set using
    feeler
    gauges but
    powder not
    laid in
    preparation
    for cleaning
    scan with no
    powder.
    1 50% Beam P = 82 W 50 μm −200 μm Cleaning
    Overlap Qs = Scan (No
    30 kHz powder.
    v =
    60 mm/s
    An =
    27.3 J/mm2
    Circular P = 82 W Powder
    profile. Qs = spread but
    5 concentric 40 kHz build
    circles, V = platform
    0.1 mm offset 160 mm/s not
    to negate An = lowered.
    effects of 5.125 J/mm2
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = same
    30 kHz powder
    v = layer as
    300 mm/s previous
    An = profile
    5.467/mm2 scan.
    2 Circular P = 82 W 100 μm  −300 μm Powder
    profile. Qs = laid as
    5 concentric 40 kHz usual
    circles, V =
    0.1 mm offset 160 mm/s
    to negate An =
    effects of 5.125 J/mm2
    ‘First
    Pulse’
    25% Beam P = 82 W Scanned on
    Overlap Qs = same
    30 kHz powder
    v = layer as
    300 mm/s previous
    An = profile
    3.644 J/mm2 scan.
    3 Circular P = 82 W 100 μm  −400 μm Powder
    profile. Qs = laid as
    5 concentric 40 kHz usual
    circles, V =
    0.1 mm offset 160 mm/s
    to negate An =
    effects of 5.125 J/mm2
    ‘First
    Pulse’
    0% Beam P = 82 W Scanned on
    Overlap Qs = same
    30 kHz powder
    v = layer as
    300 mm/s previous
    An = profile
    2.733 J/mm2 scan.
    4 Waffle 0 and P = 82 W 75 μm −475 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    5 Waffle 0 and P = 82 W 75 μm −550 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    6 Waffle 0 and P = 82 W 75 μm −625 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    7 Waffle 45 P = 82 W 75 μm −700 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    8 Waffle 45 P = 82 W 75 μm −775 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    9 Waffle 45 P = 82 W 75 μm −850 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    Ti on Ti Experimental Procedure.
    Initial Titanium Coating
    Zero
    0
    Distance
    Between
    Roller &
    Build
    Platform
    0 1st layer 50 μm  −50 μm
    thickness
    set using
    feeler
    gauges but
    powder not
    laid in
    preparation
    for
    cleaning
    scan with
    no powder.
    1 50% Beam P = 82 W Initial
    Overlap Qs = 30 kHz Cleaning
    v = 60 mm/s Scan (no
    An = powder)
    27.333 J/mm2
    Circular P = 82 W Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    2 Circular P = 82 W 50 μm −100 μm Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    3 Circular P = 82 W 50 μm −150 μm Powder
    profile. 5 Qs = 40 kHz laid as
    concentric V = usual
    circles, 160 mm/s
    0.1 mm An =
    offset to 5.125 J/mm2
    negate
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan.
    Final Titanium Coating
    1 Circular P = 82 W 100 μm  −250 μm Powder
    profile. Qs = 40 kHz laid as
    5 concentric V = usual
    circles, 160 mm/s
    0.1 mm offset An =
    to negate 5.125 J/mm2
    effects of
    ‘First
    Pulse’
    50% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    5.467 J/mm2 profile
    scan
    2 Circular P = 82 W 100 μm  −350 μm Powder
    profile. Qs = 40 kHz laid as
    5 concentric V = usual
    circles, 160 mm/s
    0.1 mm offset An =
    to negate 5.125 J/mm2
    effects of
    ‘First
    Pulse’
    25% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    3.644 J/mm2 profile
    scan.
    3 Circular P = 82 W 100 μm  −450 μm Powder
    profile. Qs = 40 kHz laid as
    5 concentric V = usual
    circles, 160 mm/s
    0.1 mm offset An =
    to negate 5.125 J/mm2
    effects of
    ‘First
    Pulse’
    0% Beam P = 82 W Scanned on
    Overlap Qs = 30 kHz same
    v = powder
    300 mm/s layer as
    An = previous
    2.733 J/mm2 profile
    scan.
    4 Waffle 0 and P = 82 W 75 μm −525 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    5 Waffle 0 and P = 82 W 75 μm −600 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    6 Waffle 0 and P = 82 W 75 μm −675 μm Powder
    90° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    7 Waffle 45 P = 82 W 75 μm −750 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    8 Waffle 45 P = 82 W 75 μm −825 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
    9 Waffle 45 P = 82 W 75 μm −900 μm Powder
    and 135° Qs = 0 Hz laid as
    700 μm (cw) usual
    linespacing v =
    (−600% Beam 240 mm/s
    overlap) An =
    0.488 J/mm2
  • The second and preferred approach uses a continuous scanning strategy whereby the pores are developed by the planar deposition of laser melted powder tracks superimposed over each other. This superimposition combined with the melt flow produces random and pseudorandom porous structures. The properties of the final structure, randomness, interconnectivity, mechanical strength and thermal response are controlled by the process parameters employed. One set of scanning parameters used was: Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45° 45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction. The array of sequences was repeated many times to give a construct of the desired height. Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of −700%. FIG. 32 shows such a construct.
  • The use of an optical inspection method to determine this approximate porosity is appropriate given the sample size. This method, although not accurate due to the filter selection process, can, if used carefully, provide an indication of porosity. An average porosity level of around 25% was predicted. This porosity level falls within the range of the desired porosity for bone in-growth structures.
  • In consideration of the potential application, it is important to minimize loose surface contamination and demonstrate the ability to fully clean the surface. Laser cleaning or acid etching technique may be effective. Additionally, a rigorous cleaning protocol to remove all loose powder may entail blowing the porous structure with clean dry compressed gas, followed by a period of ultrasonic agitation in a treatment fluid. Once dried, a laser scan may be used to seal any remaining loose particles.
  • On examination, all candidate materials and substrates were selectively fused to produce a complex interconnected pore structure. There were small differences in certain process parameters such as speed and beam overlap percentage. From FIG. 12 it can also be seen how the Ti build has successfully fused with the Ti alloy substrate using a laser power of 82 W cw, beam overlap of −40% and a laser scanning speed of 180 mms−1. With the ability to produce structures with a controlled porosity, this demonstrates how the Direct Laser Remelting process can be used as a surface modification technology. Certain metal combinations interacted unfavourably and resulted in formation of intermetallics, which are inherently brittle structures. To overcome this problem it may be necessary to use a bond coat with the substrate. It is then possible to build directly on to the substrate with a porous build. A typical example of the use of a bond coat is provided by the combination of titanium on to a cobalt chromium substrate. Tantalum also was an effective bond coat in this example. Note that the bond coat may be applied by laser technology, but other methods are also possible such as gas plasma deposition.
  • The non-contact surface profilimeotry (OSP) images shown in FIGS. 13( a) to 13(d) show the surface profile. In addition, the Surface Data shown in FIGS. 14( a) and 14(b) and 15(a) and 15(b) show a coded profile of the plan views of the samples. FIG. 14( a) shows Ti on Ti (OSP Surface Data) where v=200 mms−1, FIG. 14( b) shows CoCr on Ti (OSP Surface Data) where v=200 mms−1, and FIG. 15( a) shows Nb on Ti (OSP Surface Data) where v=200 mms−1 and FIG. 15( b) shows Ta on Ti (OSP Surface Data) where v=200 mms−1.
  • FIGS. 16 to 25 are scanning electron microscope (SEM) micrographs of a series of single layer Ti on CoCr and Ti on Ti images that were produced prior to the multi-layer builds shown in FIGS. 8 and 9 respectively and as follows.
  • FIG. 16( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=160 mms−1;
  • FIG. 16( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=160 mms−1;
  • FIG. 17( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=170 mms−1;
  • FIG. 17( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=180 mms−1;
  • FIG. 18( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=190 mms−1;
  • FIG. 18( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=200 mms−1;
  • FIG. 19( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=210 mms−1;
  • FIG. 19( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=220 mms−1;
  • FIG. 20( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=230 mms−1;
  • FIG. 20( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=240 mms−1;
  • FIG. 21( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=160 mms−1;
  • FIG. 21( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=170 mms−1;
  • FIG. 22( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=190 mms−1;
  • FIG. 22( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=200 mms−1;
  • FIG. 23( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=220 mms−1;
  • FIG. 23( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=230 mms−1;
  • FIG. 24( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=240 mms−1;
  • FIG. 24( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=240 mms−1;
  • The method according to the present invention can produce surface structures on all powder/baseplate combinations with careful selection of process parameters.
  • As described above, the process is carried out on flat baseplates that provide for easy powder delivery in successive layers of around 100 μm thickness. Control of powder layer thickness is very important if consistent surface properties are required. The application of this technology can also be applied to curved surfaces such as those found in modern prosthetic devices; with refinements being made to the powder layer technique.
  • The structures have all received ultrasonic and aqueous cleaning. On close examination, the resultant porous surfaces produced by the Direct Laser Remelting process exhibit small particulates that are scattered throughout the structure. It is unclear at this stage whether these particulates are bonded to the surface or loosely attached but there are means to remove the particulates if required.
  • The Direct Laser Remelting process has the ability to produce porous structures that are suitable for bone in-growth applications. The powdered surfaces have undergone considerable thermal cycling culminating in rapid cooling rates that have produced very fine dendritic structures (e.g. FIGS. 13( a) to 13(d)).
  • The Direct Laser Remelting process can produce effective bone in-growth surfaces and the manufacturing costs are reasonable.
  • In the preceding examples, the object has been to provide a porous structure on a base but the present invention can also be used to provide a non-porous structure on such a base to form a three-dimensional structure. The same techniques can be utilized for the materials concerned but the laser processing parameters can be appropriately selected so that a substantially solid non-porous structure is achieved.
  • Again, a technique can be used to deposit the powder onto a suitable carrier, for example a mold, and to carry out the process without the use of a base so that a three-dimensional structure is achieved which can be either porous, as described above, or non-porous if required.
  • It will be appreciated that this method can, therefore, be used to produce article from the metals referred to which can be created to a desired shape and which may or may not require subsequent machining. Yet again, such an article can be produced so that it has a graded porosity of, e.g., non-porous through various degrees of porosity to the outer surface layer. Such articles could be surgical prostheses, parts or any other article to which this method of production would be advantageous.

Claims (22)

1. A method of producing a three-dimensional porous tissue ingrowth structure comprising:
depositing a first layer of a metal powder onto a substrate;
scanning a laser beam at least once over the first layer of metal powder to remelt the metal powder in order to create at least two solid portions separated from one another so as to give a required pore size;
depositing a second layer of metal powder onto the first layer; and
repeating the laser scanning steps for each successive layer until a desired height is reached.
2. The method according to claim 1, wherein the laser beam has a power (P) in Joule per sec. with a scanning speed (v) in millimeters per sec., and a line separation (d) in millimeters such that the number calculated by the formula P/(d×v) lies between the range 0.3-8 J/mm2.
3. The method according to claim 2, wherein the laser power may be varied within a range between 5 to 1000 watts.
4. The method according to claim 1, wherein the metal powder is selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium.
5. The method according to claim 1, wherein during the step of repeating the laser scanning steps, at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
6. The method according to claim 1, wherein the thickness of each of the first layer and the successive layers of powder is between 5 μm-2000 μm.
7. The method according to claim 1, wherein the substrate is a base or core made of a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, wherein the first layer is fused to the base or core.
8. The method according to claim 7, wherein the core is integral with the resultant porous ingrowth structure and imparts additional physical properties to the overall construct.
9. The method accordingly to claim 7, wherein the core is detached from a resultant porous surface buildup.
10. The method according to claim 7, wherein a third element is added between the base and the first layer of powder to form a bond coat on the substrate.
11. The method according to claim 1, wherein the laser power is applied continuously or in a pulsed manner.
12. The method according to claim 1, wherein the method is carried out under an inert atmosphere.
13. A method of producing a three-dimensional porous tissue ingrowth structure comprising:
depositing a first layer of metal powder onto a substrate;
scanning a laser beam having a power and a diameter with a speed between approximately 100 mms−1 to 260 mms−1 and a beam overlap less than zero over the metal powder to remelt the metal powder in order to create at least two solid lines so as to give a required pore size, the negative beam overlap allowing for a non-solid space between the two solid lines; and
depositing at least one additional layer of the metal powder onto the first layer and repeating the laser scanning steps for each successive layer.
14. The method according to claim 13, wherein the metal powder is selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium.
15. The method according to claim 13, wherein the thickness of each of the layers is between 50 μm-2000 μm.
16. The method according to claim 13, wherein the substrate is a base or core made of a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, wherein the first layer is fused to the base or core.
17. The method according to claim 16, wherein the thickness of the powder is approximately 100 μm.
18. The method according to claim 13, wherein the laser power is approximately 78 W to 82 W.
19. The method according to claim 13, wherein the laser power is applied in a continuous wave or in a pulse wave.
20. The method according to claim 13, wherein the method is carried out under an inert atmosphere.
21. The method according to claim 13, comprising the additional step of subjecting a powder layer to a second laser scan with a scanning speed and beam overlap in an orthogonal direction to a first scan.
22. A method of producing a three-dimensional porous tissue ingrowth structure comprising:
providing a substrate made of a metal selected from selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium;
depositing a first layer of a metal powder onto the substrate, the metal powder selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium;
scanning a laser beam at least once over the first layer of metal powder to remelt the metal powder in order to create at least two solid portions separated from one another so as to give a required pore size;
depositing a second layer of metal powder onto the first layer; and
repeating the laser scanning steps for each successive layer until a desired height is reached,
wherein during the step of repeating the laser scanning steps, at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
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US13/605,354 US8992703B2 (en) 2002-11-08 2012-09-06 Laser-produced porous surface
US14/671,545 US10525688B2 (en) 2002-11-08 2015-03-27 Laser-produced porous surface
US16/690,307 US11155073B2 (en) 2002-11-08 2019-11-21 Laser-produced porous surface
US17/176,842 US11186077B2 (en) 2002-11-08 2021-02-16 Laser-produced porous surface
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Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110143094A1 (en) * 2009-12-11 2011-06-16 Ngimat Co. Process for Forming High Surface Area Embedded Coating with High Abrasion Resistance
US20150321289A1 (en) * 2014-05-12 2015-11-12 Siemens Energy, Inc. Laser deposition of metal foam
US20170021453A1 (en) * 2013-12-23 2017-01-26 General Electric Technology Gmbh Gamma prime precipitation strengthened nickel-base superalloy for use in powder based additive manufacturing process
WO2021097248A1 (en) * 2019-11-14 2021-05-20 University Of Washington Closed-loop feedback for additive manufacturing simulation
US11167375B2 (en) 2018-08-10 2021-11-09 The Research Foundation For The State University Of New York Additive manufacturing processes and additively manufactured products
EP2817037B1 (en) * 2012-02-20 2022-08-03 Smith & Nephew, Inc. Methods of making porous structures
US11897033B2 (en) 2018-04-19 2024-02-13 Compagnie Generale Des Etablissements Michelin Process for the additive manufacturing of a three-dimensional metal part

Families Citing this family (343)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2836282B1 (en) * 2002-02-19 2004-04-02 Commissariat Energie Atomique ALVEOLAR STRUCTURE AND METHOD OF MANUFACTURING SUCH A STRUCTURE
US20060147332A1 (en) 2004-12-30 2006-07-06 Howmedica Osteonics Corp. Laser-produced porous structure
EP1418013B1 (en) 2002-11-08 2005-01-19 Howmedica Osteonics Corp. Laser-produced porous surface
US7666522B2 (en) * 2003-12-03 2010-02-23 IMDS, Inc. Laser based metal deposition (LBMD) of implant structures
US7001672B2 (en) * 2003-12-03 2006-02-21 Medicine Lodge, Inc. Laser based metal deposition of implant structures
US20070106374A1 (en) * 2004-01-22 2007-05-10 Isoflux, Inc. Radiopaque coating for biomedical devices
US20180228621A1 (en) 2004-08-09 2018-08-16 Mark A. Reiley Apparatus, systems, and methods for the fixation or fusion of bone
GB0422666D0 (en) * 2004-10-12 2004-11-10 Benoist Girard Sas Prosthetic acetabular cups
US20060133947A1 (en) * 2004-12-21 2006-06-22 United Technologies Corporation Laser enhancements of cold sprayed deposits
FR2884406B1 (en) 2005-04-14 2008-10-17 Memometal Technologies Soc Par INTRAMEDULAR OSTEOSYNTHESIS DEVICE OF TWO BONE PARTS, IN PARTICULAR HAND AND / OR FOOT
DE102005024913A1 (en) 2005-05-31 2006-12-14 Axetis Ag Stent for insertion into vessel, comprises specifically applied coating for avoidance of new blockage
GB0511460D0 (en) 2005-06-06 2005-07-13 Univ Liverpool Process
ITMI20051717A1 (en) * 2005-09-16 2007-03-17 Leader Italia S R L DENTAL ENDOSSEO PLANT STRUCTURE WITH DEFAULT GEOMETRY SURFACE
DE102005045699A1 (en) * 2005-09-20 2007-03-29 Michael Haas Die casting method employs mold with areas of different thermal conductivity, setting up different rates of heat dissipation from casting
US20070085241A1 (en) * 2005-10-14 2007-04-19 Northrop Grumman Corporation High density performance process
DE102005049886A1 (en) * 2005-10-17 2007-04-19 Sirona Dental Systems Gmbh Tooth replacement part manufacturing method involves energy beam sintering powder material at the edge area to a greater density than in inner region by varying process parameters during sintering
DE102005050665A1 (en) * 2005-10-20 2007-04-26 Bego Medical Gmbh Layer-wise production process with grain size influencing
US8728387B2 (en) 2005-12-06 2014-05-20 Howmedica Osteonics Corp. Laser-produced porous surface
US7648524B2 (en) * 2005-12-23 2010-01-19 Howmedica Osteonics Corp. Porous tendon anchor
US20070179607A1 (en) * 2006-01-31 2007-08-02 Zimmer Technology, Inc. Cartilage resurfacing implant
GB0601982D0 (en) * 2006-02-01 2006-03-15 Rolls Royce Plc Method and apparatus for examination of objects and structures
US9327056B2 (en) * 2006-02-14 2016-05-03 Washington State University Bone replacement materials
US8603180B2 (en) 2006-02-27 2013-12-10 Biomet Manufacturing, Llc Patient-specific acetabular alignment guides
US8591516B2 (en) 2006-02-27 2013-11-26 Biomet Manufacturing, Llc Patient-specific orthopedic instruments
US20150335438A1 (en) 2006-02-27 2015-11-26 Biomet Manufacturing, Llc. Patient-specific augments
US8568487B2 (en) 2006-02-27 2013-10-29 Biomet Manufacturing, Llc Patient-specific hip joint devices
US9173661B2 (en) 2006-02-27 2015-11-03 Biomet Manufacturing, Llc Patient specific alignment guide with cutting surface and laser indicator
US8407067B2 (en) 2007-04-17 2013-03-26 Biomet Manufacturing Corp. Method and apparatus for manufacturing an implant
US8608749B2 (en) 2006-02-27 2013-12-17 Biomet Manufacturing, Llc Patient-specific acetabular guides and associated instruments
US9345548B2 (en) 2006-02-27 2016-05-24 Biomet Manufacturing, Llc Patient-specific pre-operative planning
US8535387B2 (en) 2006-02-27 2013-09-17 Biomet Manufacturing, Llc Patient-specific tools and implants
US8092465B2 (en) 2006-06-09 2012-01-10 Biomet Manufacturing Corp. Patient specific knee alignment guide and associated method
US9339278B2 (en) 2006-02-27 2016-05-17 Biomet Manufacturing, Llc Patient-specific acetabular guides and associated instruments
US8608748B2 (en) 2006-02-27 2013-12-17 Biomet Manufacturing, Llc Patient specific guides
US9918740B2 (en) 2006-02-27 2018-03-20 Biomet Manufacturing, Llc Backup surgical instrument system and method
US9113971B2 (en) 2006-02-27 2015-08-25 Biomet Manufacturing, Llc Femoral acetabular impingement guide
US8377066B2 (en) 2006-02-27 2013-02-19 Biomet Manufacturing Corp. Patient-specific elbow guides and associated methods
US9907659B2 (en) 2007-04-17 2018-03-06 Biomet Manufacturing, Llc Method and apparatus for manufacturing an implant
US9289253B2 (en) 2006-02-27 2016-03-22 Biomet Manufacturing, Llc Patient-specific shoulder guide
US7967868B2 (en) 2007-04-17 2011-06-28 Biomet Manufacturing Corp. Patient-modified implant and associated method
US10278711B2 (en) 2006-02-27 2019-05-07 Biomet Manufacturing, Llc Patient-specific femoral guide
US7951412B2 (en) * 2006-06-07 2011-05-31 Medicinelodge Inc. Laser based metal deposition (LBMD) of antimicrobials to implant surfaces
US9795399B2 (en) 2006-06-09 2017-10-24 Biomet Manufacturing, Llc Patient-specific knee alignment guide and associated method
US8147861B2 (en) * 2006-08-15 2012-04-03 Howmedica Osteonics Corp. Antimicrobial implant
GB2442441B (en) * 2006-10-03 2011-11-09 Biomet Uk Ltd Surgical instrument
US7866372B2 (en) * 2006-12-20 2011-01-11 The Boeing Company Method of making a heat exchanger core component
US7810552B2 (en) * 2006-12-20 2010-10-12 The Boeing Company Method of making a heat exchanger
US7866377B2 (en) * 2006-12-20 2011-01-11 The Boeing Company Method of using minimal surfaces and minimal skeletons to make heat exchanger components
ITUD20070092A1 (en) * 2007-05-29 2008-11-30 Lima Lto S P A PROSTHETIC ELEMENT AND RELATIVE PROCEDURE FOR IMPLEMENTATION
EP2022447A1 (en) * 2007-07-09 2009-02-11 Astra Tech AB Nanosurface
US10758283B2 (en) 2016-08-11 2020-09-01 Mighty Oak Medical, Inc. Fixation devices having fenestrations and methods for using the same
WO2009014718A1 (en) 2007-07-24 2009-01-29 Porex Corporation Porous laser sintered articles
EP2231352B1 (en) 2008-01-03 2013-10-16 Arcam Ab Method and apparatus for producing three-dimensional objects
GB0809721D0 (en) * 2008-05-28 2008-07-02 Univ Bath Improvements in or relating to joints and/or implants
US20100042218A1 (en) * 2008-08-13 2010-02-18 Nebosky Paul S Orthopaedic implant with porous structural member
JP5774989B2 (en) 2008-08-13 2015-09-09 スメド−ティーエイ/ティーディー・エルエルシー Orthopedic screw
US9616205B2 (en) 2008-08-13 2017-04-11 Smed-Ta/Td, Llc Drug delivery implants
US20100042213A1 (en) 2008-08-13 2010-02-18 Nebosky Paul S Drug delivery implants
US9700431B2 (en) 2008-08-13 2017-07-11 Smed-Ta/Td, Llc Orthopaedic implant with porous structural member
US10842645B2 (en) 2008-08-13 2020-11-24 Smed-Ta/Td, Llc Orthopaedic implant with porous structural member
JP5687622B2 (en) 2008-08-29 2015-03-18 スメド−ティーエイ/ティーディー・エルエルシー Orthopedic implant
FR2935601B1 (en) 2008-09-09 2010-10-01 Memometal Technologies INTRAMEDULLARY IMPLANT RESORBABLE BETWEEN TWO BONE OR TWO BONE FRAGMENTS
DE102009014184A1 (en) * 2008-11-07 2010-05-20 Advanced Medical Technologies Ag Implant for fusion of spinal segments
US8821555B2 (en) 2009-02-11 2014-09-02 Howmedica Osteonics Corp. Intervertebral implant with integrated fixation
CA2753201C (en) 2009-02-24 2019-03-19 Mako Surgical Corp. Prosthetic device, method of planning bone removal for implantation of prosthetic device, and robotic system
US9220547B2 (en) 2009-03-27 2015-12-29 Spinal Elements, Inc. Flanged interbody fusion device
EP2424707B2 (en) 2009-04-28 2021-09-29 BAE Systems PLC Additive layer fabrication method
ES2663554T5 (en) 2009-04-28 2022-05-06 Bae Systems Plc Layered additive manufacturing method
EP2253291B1 (en) 2009-05-19 2016-03-16 National University of Ireland, Galway A bone implant with a surface anchoring structure
US20180253774A1 (en) * 2009-05-19 2018-09-06 Cobra Golf Incorporated Method and system for making golf club components
GB0910447D0 (en) 2009-06-17 2009-07-29 Ulive Entpr Ltd Dental implant
US9399321B2 (en) 2009-07-15 2016-07-26 Arcam Ab Method and apparatus for producing three-dimensional objects
DE102009028503B4 (en) 2009-08-13 2013-11-14 Biomet Manufacturing Corp. Resection template for the resection of bones, method for producing such a resection template and operation set for performing knee joint surgery
WO2011022560A1 (en) 2009-08-19 2011-02-24 Smith & Nephew, Inc. Porous implant structures
DE102009043597A1 (en) * 2009-09-25 2011-04-07 Siemens Aktiengesellschaft Method for producing a marked object
KR20120095377A (en) * 2009-10-07 2012-08-28 바이오2 테크놀로지스, 아이엔씨. Devices and methods for tissue engineering
FR2951971B1 (en) * 2009-11-03 2011-12-09 Michelin Soc Tech SUPPORT PLATE FOR LASER SINTERING DEVICE AND IMPROVED SINKING METHOD
RU2627454C2 (en) * 2009-11-12 2017-08-08 Смит Энд Нефью, Инк. Porous structures with controllable randomization and methods for their production
JP4802277B2 (en) * 2009-12-28 2011-10-26 ナカシマメディカル株式会社 Shock absorbing structure and manufacturing method thereof
FR2955025B1 (en) * 2010-01-11 2012-11-30 Kasios POROUS TITANIUM PIECE AND METHOD OF MANUFACTURING THE SAME
DE102010008960A1 (en) * 2010-02-23 2011-08-25 EOS GmbH Electro Optical Systems, 82152 Method and device for producing a three-dimensional object that is particularly suitable for use in microtechnology
US8632547B2 (en) 2010-02-26 2014-01-21 Biomet Sports Medicine, Llc Patient-specific osteotomy devices and methods
IT1398443B1 (en) * 2010-02-26 2013-02-22 Lima Lto S P A Ora Limacorporate Spa INTEGRATED PROSTHETIC ELEMENT
US8468673B2 (en) 2010-09-10 2013-06-25 Bio2 Technologies, Inc. Method of fabricating a porous orthopedic implant
US9271744B2 (en) 2010-09-29 2016-03-01 Biomet Manufacturing, Llc Patient-specific guide for partial acetabular socket replacement
US8535386B2 (en) 2010-10-21 2013-09-17 Howmedica Osteonics Corp. Stem with pressfit porous element
CA2818195C (en) 2010-11-18 2018-12-18 Zimmer, Inc. Resistance welding a porous metal layer to a metal substrate
US10427235B2 (en) * 2010-11-18 2019-10-01 Zimmer, Inc. Resistance welding a porous metal layer to a metal substrate
US9968376B2 (en) 2010-11-29 2018-05-15 Biomet Manufacturing, Llc Patient-specific orthopedic instruments
DE102010063725B4 (en) * 2010-12-21 2015-10-08 Siemens Aktiengesellschaft Component with a filled cavity, use of this component and method for its preparation
US9073265B2 (en) 2011-01-28 2015-07-07 Arcam Ab Method for production of a three-dimensional body
US9241745B2 (en) 2011-03-07 2016-01-26 Biomet Manufacturing, Llc Patient-specific femoral version guide
US8715289B2 (en) 2011-04-15 2014-05-06 Biomet Manufacturing, Llc Patient-specific numerically controlled instrument
US8668700B2 (en) 2011-04-29 2014-03-11 Biomet Manufacturing, Llc Patient-specific convertible guides
US8956364B2 (en) 2011-04-29 2015-02-17 Biomet Manufacturing, Llc Patient-specific partial knee guides and other instruments
US8532807B2 (en) 2011-06-06 2013-09-10 Biomet Manufacturing, Llc Pre-operative planning and manufacturing method for orthopedic procedure
US9084618B2 (en) 2011-06-13 2015-07-21 Biomet Manufacturing, Llc Drill guides for confirming alignment of patient-specific alignment guides
CA2839706C (en) 2011-06-23 2017-05-02 Stryker Corporation Prosthetic implant and method of implantation
US8764760B2 (en) 2011-07-01 2014-07-01 Biomet Manufacturing, Llc Patient-specific bone-cutting guidance instruments and methods
US20130001121A1 (en) 2011-07-01 2013-01-03 Biomet Manufacturing Corp. Backup kit for a patient-specific arthroplasty kit assembly
US8597365B2 (en) 2011-08-04 2013-12-03 Biomet Manufacturing, Llc Patient-specific pelvic implants for acetabular reconstruction
US9295497B2 (en) 2011-08-31 2016-03-29 Biomet Manufacturing, Llc Patient-specific sacroiliac and pedicle guides
US9066734B2 (en) 2011-08-31 2015-06-30 Biomet Manufacturing, Llc Patient-specific sacroiliac guides and associated methods
US9386993B2 (en) 2011-09-29 2016-07-12 Biomet Manufacturing, Llc Patient-specific femoroacetabular impingement instruments and methods
US9451973B2 (en) 2011-10-27 2016-09-27 Biomet Manufacturing, Llc Patient specific glenoid guide
KR20130046336A (en) 2011-10-27 2013-05-07 삼성전자주식회사 Multi-view device of display apparatus and contol method thereof, and display system
US9301812B2 (en) 2011-10-27 2016-04-05 Biomet Manufacturing, Llc Methods for patient-specific shoulder arthroplasty
EP3384858A1 (en) 2011-10-27 2018-10-10 Biomet Manufacturing, LLC Patient-specific glenoid guides
US9554910B2 (en) 2011-10-27 2017-01-31 Biomet Manufacturing, Llc Patient-specific glenoid guide and implants
US9011444B2 (en) 2011-12-09 2015-04-21 Howmedica Osteonics Corp. Surgical reaming instrument for shaping a bone cavity
EP2793756B1 (en) 2011-12-23 2019-05-08 The Royal Institution for the Advancement of Learning / McGill University Bone replacement implants with mechanically biocompatible cellular material
WO2013098135A1 (en) * 2011-12-28 2013-07-04 Arcam Ab Method and apparatus for manufacturing porous three-dimensional articles
EP2797730B2 (en) 2011-12-28 2020-03-04 Arcam Ab Method and apparatus for detecting defects in freeform fabrication
US9079248B2 (en) 2011-12-28 2015-07-14 Arcam Ab Method and apparatus for increasing the resolution in additively manufactured three-dimensional articles
AU2012362279A1 (en) 2011-12-30 2014-07-24 Howmedica Osteonics Corp. Systems for preparing bone voids to receive a prosthesis
US11304811B2 (en) 2012-01-17 2022-04-19 KYOCERA Medical Technologies, Inc. Surgical implant devices incorporating porous surfaces and associated method of manufacture
US10765530B2 (en) 2012-06-21 2020-09-08 Renovis Surgical Technologies, Inc. Surgical implant devices incorporating porous surfaces
CN104168854B (en) * 2012-01-24 2017-02-22 史密夫和内修有限公司 Porous structure and methods of making same
US9237950B2 (en) 2012-02-02 2016-01-19 Biomet Manufacturing, Llc Implant with patient-specific porous structure
US9364896B2 (en) 2012-02-07 2016-06-14 Medical Modeling Inc. Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology
US10363140B2 (en) 2012-03-09 2019-07-30 Si-Bone Inc. Systems, device, and methods for joint fusion
WO2013134670A1 (en) 2012-03-09 2013-09-12 Si-Bone Inc. Integrated implant
US9180010B2 (en) 2012-04-06 2015-11-10 Howmedica Osteonics Corp. Surface modified unit cell lattice structures for optimized secure freeform fabrication
US9135374B2 (en) 2012-04-06 2015-09-15 Howmedica Osteonics Corp. Surface modified unit cell lattice structures for optimized secure freeform fabrication
ES2828357T3 (en) 2012-05-04 2021-05-26 Si Bone Inc Fenestrated implant
US9126167B2 (en) 2012-05-11 2015-09-08 Arcam Ab Powder distribution in additive manufacturing
US10154913B2 (en) 2012-06-21 2018-12-18 Renovis Surgical Technologies, Inc. Surgical implant devices incorporating porous surfaces and a locking plate
US8900303B2 (en) 2012-07-09 2014-12-02 Howmedica Osteonics Corp. Porous bone reinforcements
US8843229B2 (en) * 2012-07-20 2014-09-23 Biomet Manufacturing, Llc Metallic structures having porous regions from imaged bone at pre-defined anatomic locations
US9415137B2 (en) * 2012-08-22 2016-08-16 Biomet Manufacturing, Llc. Directional porous coating
US20140067080A1 (en) * 2012-09-05 2014-03-06 Christopher G. Sidebotham Hip stem prosthesis with a porous collar to allow for bone ingrowth
US20140076749A1 (en) * 2012-09-14 2014-03-20 Raytheon Company Variable density desiccator housing and method of manufacturing
EP2916980B1 (en) 2012-11-06 2016-06-01 Arcam Ab Powder pre-processing for additive manufacturing
US9060788B2 (en) 2012-12-11 2015-06-23 Biomet Manufacturing, Llc Patient-specific acetabular guide for anterior approach
US9907654B2 (en) * 2012-12-11 2018-03-06 Dr. H.C. Robert Mathys Stiftung Bone substitute and method for producing the same
US9204977B2 (en) 2012-12-11 2015-12-08 Biomet Manufacturing, Llc Patient-specific acetabular guide for anterior approach
DE112013006029T5 (en) 2012-12-17 2015-09-17 Arcam Ab Method and device for additive manufacturing
WO2014095200A1 (en) 2012-12-17 2014-06-26 Arcam Ab Additive manufacturing method and apparatus
US9763791B2 (en) 2013-02-06 2017-09-19 Howmedica Osteonics Corp. Femoral prosthesis head
EP2964802A4 (en) * 2013-03-05 2016-11-02 Pcc Structurals Inc BONDING OF TITANIUM COATING TO CAST CoCr
US9949837B2 (en) 2013-03-07 2018-04-24 Howmedica Osteonics Corp. Partially porous bone implant keel
WO2014137876A2 (en) 2013-03-08 2014-09-12 Stryker Corporation Bone pads
US9839438B2 (en) 2013-03-11 2017-12-12 Biomet Manufacturing, Llc Patient-specific glenoid guide with a reusable guide holder
US9579107B2 (en) 2013-03-12 2017-02-28 Biomet Manufacturing, Llc Multi-point fit for patient specific guide
US9498233B2 (en) 2013-03-13 2016-11-22 Biomet Manufacturing, Llc. Universal acetabular guide and associated hardware
US9826981B2 (en) 2013-03-13 2017-11-28 Biomet Manufacturing, Llc Tangential fit of patient-specific guides
US9526513B2 (en) 2013-03-13 2016-12-27 Howmedica Osteonics Corp. Void filling joint prosthesis and associated instruments
US9517145B2 (en) 2013-03-15 2016-12-13 Biomet Manufacturing, Llc Guide alignment system and method
JP2016513551A (en) 2013-03-15 2016-05-16 マコ サージカル コーポレーション Unicondylar tibial knee implant
US9408699B2 (en) 2013-03-15 2016-08-09 Smed-Ta/Td, Llc Removable augment for medical implant
US9681966B2 (en) 2013-03-15 2017-06-20 Smed-Ta/Td, Llc Method of manufacturing a tubular medical implant
US9724203B2 (en) 2013-03-15 2017-08-08 Smed-Ta/Td, Llc Porous tissue ingrowth structure
US9550207B2 (en) 2013-04-18 2017-01-24 Arcam Ab Method and apparatus for additive manufacturing
US9676031B2 (en) 2013-04-23 2017-06-13 Arcam Ab Method and apparatus for forming a three-dimensional article
US9415443B2 (en) 2013-05-23 2016-08-16 Arcam Ab Method and apparatus for additive manufacturing
US9468973B2 (en) 2013-06-28 2016-10-18 Arcam Ab Method and apparatus for additive manufacturing
CN105578994B (en) * 2013-07-24 2019-08-02 雷诺维斯外科技术公司 Combine the surgical implant device of porous surface
US10016811B2 (en) * 2013-08-09 2018-07-10 David J. Neal Orthopedic implants and methods of manufacturing orthopedic implants
WO2015073081A1 (en) * 2013-08-20 2015-05-21 The Trustees Of Princeton University Density enhancement methods and compositions
US9505057B2 (en) 2013-09-06 2016-11-29 Arcam Ab Powder distribution in additive manufacturing of three-dimensional articles
US9676032B2 (en) 2013-09-20 2017-06-13 Arcam Ab Method for additive manufacturing
EP3052037B1 (en) * 2013-10-02 2022-08-24 Kyocera Medical Technologies, Inc. Surgical implant devices incorporating porous surfaces and a locking plate
US20150112349A1 (en) 2013-10-21 2015-04-23 Biomet Manufacturing, Llc Ligament Guide Registration
US10434572B2 (en) 2013-12-19 2019-10-08 Arcam Ab Method for additive manufacturing
US9802253B2 (en) 2013-12-16 2017-10-31 Arcam Ab Additive manufacturing of three-dimensional articles
US10130993B2 (en) 2013-12-18 2018-11-20 Arcam Ab Additive manufacturing of three-dimensional articles
US9789563B2 (en) 2013-12-20 2017-10-17 Arcam Ab Method for additive manufacturing
EP3092096A4 (en) * 2014-01-09 2017-03-08 United Technologies Corporation Material and processes for additively manufacturing one or more parts
US9789541B2 (en) 2014-03-07 2017-10-17 Arcam Ab Method for additive manufacturing of three-dimensional articles
US20150283613A1 (en) 2014-04-02 2015-10-08 Arcam Ab Method for fusing a workpiece
US10282488B2 (en) 2014-04-25 2019-05-07 Biomet Manufacturing, Llc HTO guide with optional guided ACL/PCL tunnels
US10842634B2 (en) 2014-05-02 2020-11-24 The Royal Institution For The Advancement Of Learning/Mcgill University Structural porous biomaterial and implant formed of same
US9408616B2 (en) 2014-05-12 2016-08-09 Biomet Manufacturing, Llc Humeral cut guide
US10111753B2 (en) 2014-05-23 2018-10-30 Titan Spine, Inc. Additive and subtractive manufacturing process for producing implants with homogeneous body substantially free of pores and inclusions
US9839436B2 (en) 2014-06-03 2017-12-12 Biomet Manufacturing, Llc Patient-specific glenoid depth control
US9561040B2 (en) 2014-06-03 2017-02-07 Biomet Manufacturing, Llc Patient-specific glenoid depth control
GB2541833B (en) * 2014-06-05 2021-03-17 Ossis Ltd Improvements to implant surfaces
US10687956B2 (en) 2014-06-17 2020-06-23 Titan Spine, Inc. Corpectomy implants with roughened bioactive lateral surfaces
BE1022586B1 (en) * 2014-06-18 2016-06-10 Cenat Bvba DEVICE AND METHOD FOR ADDITIVE PRODUCTION
US10327916B2 (en) 2014-07-03 2019-06-25 Howmedica Osteonics Corp. Impact absorbing pad
RU2571245C1 (en) * 2014-07-22 2015-12-20 Федеральное государственное бюджетное образовательное учреждение высшего профессионального образования "Сибирский государственный индустриальный университет" Surface hardening of 20x13 steel
US10561456B2 (en) 2014-07-24 2020-02-18 KYOCERA Medical Technologies, Inc. Bone screw incorporating a porous surface formed by an additive manufacturing process
CN104207867B (en) * 2014-08-13 2017-02-22 中国科学院福建物质结构研究所 Low-modulus medical implant porous scaffold structure
US9341467B2 (en) 2014-08-20 2016-05-17 Arcam Ab Energy beam position verification
US10166033B2 (en) 2014-09-18 2019-01-01 Si-Bone Inc. Implants for bone fixation or fusion
US9833245B2 (en) 2014-09-29 2017-12-05 Biomet Sports Medicine, Llc Tibial tubercule osteotomy
US9826994B2 (en) 2014-09-29 2017-11-28 Biomet Manufacturing, Llc Adjustable glenoid pin insertion guide
JP6174655B2 (en) 2014-10-21 2017-08-02 ユナイテッド テクノロジーズ コーポレイションUnited Technologies Corporation Ducted heat exchanger system for gas turbine engine and method for manufacturing heat exchanger for gas turbine engine
CN105525992B (en) 2014-10-21 2020-04-14 联合工艺公司 Additive manufactured ducted heat exchanger system with additive manufactured cowling
US20160143663A1 (en) 2014-11-24 2016-05-26 Stryker European Holdings I, Llc Strut plate and cabling system
US20160167303A1 (en) 2014-12-15 2016-06-16 Arcam Ab Slicing method
US10299929B2 (en) 2015-01-12 2019-05-28 Howmedica Osteonics Corp. Bone void forming apparatus
AU2016200179B2 (en) 2015-01-14 2020-09-17 Stryker European Operations Holdings Llc Spinal implant with porous and solid surfaces
CA2917503A1 (en) 2015-01-14 2016-07-14 Stryker European Holdings I, Llc Spinal implant with fluid delivery capabilities
US9721755B2 (en) 2015-01-21 2017-08-01 Arcam Ab Method and device for characterizing an electron beam
US10070962B1 (en) 2015-02-13 2018-09-11 Nextstep Arthropedix, LLC Medical implants having desired surface features and methods of manufacturing
US9820868B2 (en) 2015-03-30 2017-11-21 Biomet Manufacturing, Llc Method and apparatus for a pin apparatus
US11014161B2 (en) 2015-04-21 2021-05-25 Arcam Ab Method for additive manufacturing
US9918849B2 (en) 2015-04-29 2018-03-20 Institute for Musculoskeletal Science and Education, Ltd. Coiled implants and systems and methods of use thereof
US10449051B2 (en) 2015-04-29 2019-10-22 Institute for Musculoskeletal Science and Education, Ltd. Implant with curved bone contacting elements
CA2930123A1 (en) 2015-05-18 2016-11-18 Stryker European Holdings I, Llc Partially resorbable implants and methods
CN107835669A (en) 2015-05-22 2018-03-23 Ebm融合解决方案有限责任公司 Joint or section bone implant for malformation correction
GB201509284D0 (en) * 2015-05-29 2015-07-15 M & I Materials Ltd Selective laser melting
US10568647B2 (en) 2015-06-25 2020-02-25 Biomet Manufacturing, Llc Patient-specific humeral guide designs
US10226262B2 (en) 2015-06-25 2019-03-12 Biomet Manufacturing, Llc Patient-specific humeral guide designs
US10807187B2 (en) 2015-09-24 2020-10-20 Arcam Ab X-ray calibration standard object
US11571748B2 (en) 2015-10-15 2023-02-07 Arcam Ab Method and apparatus for producing a three-dimensional article
US10525531B2 (en) 2015-11-17 2020-01-07 Arcam Ab Additive manufacturing of three-dimensional articles
US10610930B2 (en) 2015-11-18 2020-04-07 Arcam Ab Additive manufacturing of three-dimensional articles
AU2016355581B2 (en) 2015-11-20 2022-09-08 Titan Spine, Inc. Processes for additively manufacturing orthopedic implants
TWI726940B (en) 2015-11-20 2021-05-11 美商泰坦脊柱股份有限公司 Processes for additively manufacturing orthopedic implants
US10596660B2 (en) 2015-12-15 2020-03-24 Howmedica Osteonics Corp. Porous structures produced by additive layer manufacturing
KR20180095853A (en) 2015-12-16 2018-08-28 너바시브 인코퍼레이티드 Porous Spine Fusion Implant
WO2017117527A1 (en) * 2015-12-30 2017-07-06 Mott Corporation Porous devices made by laser additive manufacturing
US10831180B2 (en) * 2016-02-25 2020-11-10 General Electric Company Multivariate statistical process control of laser powder bed additive manufacturing
US11247274B2 (en) 2016-03-11 2022-02-15 Arcam Ab Method and apparatus for forming a three-dimensional article
AU2017202311B2 (en) 2016-04-07 2022-03-03 Howmedica Osteonics Corp. Expandable interbody implant
EP3245982B1 (en) 2016-05-20 2023-11-01 Howmedica Osteonics Corp. Expandable interbody implant with lordosis correction
US10549348B2 (en) 2016-05-24 2020-02-04 Arcam Ab Method for additive manufacturing
US11325191B2 (en) 2016-05-24 2022-05-10 Arcam Ab Method for additive manufacturing
US10525547B2 (en) 2016-06-01 2020-01-07 Arcam Ab Additive manufacturing of three-dimensional articles
EP3251621B1 (en) 2016-06-03 2021-01-20 Stryker European Holdings I, LLC Intramedullary implant
US10765975B2 (en) * 2016-07-01 2020-09-08 Caterpillar Inc. Filter element and method of manufacturing a filter element
AU2017204355B2 (en) 2016-07-08 2021-09-09 Mako Surgical Corp. Scaffold for alloprosthetic composite implant
US10456262B2 (en) 2016-08-02 2019-10-29 Howmedica Osteonics Corp. Patient-specific implant flanges with bone side porous ridges
EP3493768A1 (en) 2016-08-03 2019-06-12 Titan Spine, Inc. Implant surfaces that enhance osteoinduction
US10743890B2 (en) 2016-08-11 2020-08-18 Mighty Oak Medical, Inc. Drill apparatus and surgical fixation devices and methods for using the same
US10639160B2 (en) 2016-08-24 2020-05-05 Howmedica Osteonics Corp. Peek femoral component with segmented TI foam in-growth
US10478312B2 (en) 2016-10-25 2019-11-19 Institute for Musculoskeletal Science and Education, Ltd. Implant with protected fusion zones
US10792757B2 (en) 2016-10-25 2020-10-06 Arcam Ab Method and apparatus for additive manufacturing
US11033394B2 (en) 2016-10-25 2021-06-15 Institute for Musculoskeletal Science and Education, Ltd. Implant with multi-layer bone interfacing lattice
CN106344221A (en) * 2016-10-26 2017-01-25 四川大学 Bonelike porous biomechanical bionic designed spinal fusion device and preparation method and use thereof
US10987752B2 (en) 2016-12-21 2021-04-27 Arcam Ab Additive manufacturing of three-dimensional articles
CN106735174B (en) * 2016-12-29 2019-05-28 东莞深圳清华大学研究院创新中心 A kind of 3D printing metal-base composites and preparation method thereof
EP3573553A1 (en) 2017-01-27 2019-12-04 Zimmer, Inc. Porous fixation devices and methods
WO2018143841A2 (en) * 2017-02-01 2018-08-09 ПОПОВ, Дмитрий Александрович Bone tissue augmentation for cancellous bone and articular surface replacement
US11406502B2 (en) 2017-03-02 2022-08-09 Optimotion Implants LLC Orthopedic implants and methods
US10905436B2 (en) 2017-03-02 2021-02-02 Optimotion Implants, Llc Knee arthroplasty systems and methods
US10940024B2 (en) 2017-07-26 2021-03-09 Optimotion Implants LLC Universal femoral trial system and methods
US10357377B2 (en) 2017-03-13 2019-07-23 Institute for Musculoskeletal Science and Education, Ltd. Implant with bone contacting elements having helical and undulating planar geometries
US10512549B2 (en) 2017-03-13 2019-12-24 Institute for Musculoskeletal Science and Education, Ltd. Implant with structural members arranged around a ring
US10722310B2 (en) 2017-03-13 2020-07-28 Zimmer Biomet CMF and Thoracic, LLC Virtual surgery planning system and method
US11059123B2 (en) 2017-04-28 2021-07-13 Arcam Ab Additive manufacturing of three-dimensional articles
AU2018203479A1 (en) 2017-05-18 2018-12-06 Howmedica Osteonics Corp. High fatigue strength porous structure
EP3415108A1 (en) 2017-05-25 2018-12-19 Stryker European Holdings I, LLC Fusion cage with integrated fixation and insertion features
US10940666B2 (en) 2017-05-26 2021-03-09 Howmedica Osteonics Corp. Packaging structures and additive manufacturing thereof
US11292062B2 (en) 2017-05-30 2022-04-05 Arcam Ab Method and device for producing three-dimensional objects
US10646345B2 (en) 2017-06-02 2020-05-12 Howmedica Osteonics Corp. Implant with hole having porous structure for soft tissue fixation
EP3412252B1 (en) 2017-06-09 2020-02-12 Howmedica Osteonics Corp. Polymer interlock support structure
US11628517B2 (en) 2017-06-15 2023-04-18 Howmedica Osteonics Corp. Porous structures produced by additive layer manufacturing
US11006981B2 (en) 2017-07-07 2021-05-18 K2M, Inc. Surgical implant and methods of additive manufacturing
CN107498045B (en) * 2017-08-07 2019-05-14 华南理工大学 A kind of increasing material manufacturing method of the high-strength brass alloys of leadless environment-friendly
CN111051046B (en) * 2017-08-31 2022-02-15 惠普发展公司,有限责任合伙企业 Printer with a movable platen
EP3456294A1 (en) 2017-09-15 2019-03-20 Stryker European Holdings I, LLC Intervertebral body fusion device expanded with hardening material
EP3459502A1 (en) 2017-09-20 2019-03-27 Stryker European Holdings I, LLC Spinal implants
US10828077B2 (en) 2017-09-22 2020-11-10 Howmedica Osteonics Corp. Distal radius wedge screw
EP3687422A4 (en) 2017-09-26 2021-09-22 SI-Bone, Inc. Systems and methods for decorticating the sacroiliac joint
US20190099809A1 (en) 2017-09-29 2019-04-04 Arcam Ab Method and apparatus for additive manufacturing
US11737880B2 (en) 2017-10-03 2023-08-29 Howmedica Osteonics Corp. Integrated spring for soft tissue attachment
EP3479798B1 (en) 2017-11-03 2023-06-21 Howmedica Osteonics Corp. Flexible construct for femoral reconstruction
US10529070B2 (en) 2017-11-10 2020-01-07 Arcam Ab Method and apparatus for detecting electron beam source filament wear
US10940015B2 (en) 2017-11-21 2021-03-09 Institute for Musculoskeletal Science and Education, Ltd. Implant with improved flow characteristics
US10744001B2 (en) 2017-11-21 2020-08-18 Institute for Musculoskeletal Science and Education, Ltd. Implant with improved bone contact
US11072117B2 (en) 2017-11-27 2021-07-27 Arcam Ab Platform device
US10821721B2 (en) 2017-11-27 2020-11-03 Arcam Ab Method for analysing a build layer
EP3501432A1 (en) 2017-12-20 2019-06-26 Stryker European Holdings I, LLC Joint instrumentation
US11517975B2 (en) 2017-12-22 2022-12-06 Arcam Ab Enhanced electron beam generation
WO2019140240A1 (en) 2018-01-11 2019-07-18 K2M, Inc. Implants and instruments with flexible features
US11284927B2 (en) 2018-02-02 2022-03-29 Stryker European Holdings I, Llc Orthopedic screw and porous structures thereof
US10800101B2 (en) 2018-02-27 2020-10-13 Arcam Ab Compact build tank for an additive manufacturing apparatus
US11267051B2 (en) 2018-02-27 2022-03-08 Arcam Ab Build tank for an additive manufacturing apparatus
US10932911B2 (en) 2018-03-01 2021-03-02 Biomedtrix, Llc Implant for osteotomy and canine osteotomy method
EP3773342A1 (en) 2018-03-26 2021-02-17 DePuy Synthes Products, Inc. Three-dimensional porous structures for bone ingrowth and methods for producing
US11400519B2 (en) 2018-03-29 2022-08-02 Arcam Ab Method and device for distributing powder material
WO2019186505A1 (en) 2018-03-30 2019-10-03 DePuy Synthes Products, Inc. Hybrid fixation features for three-dimensional porous structures for bone ingrowth and methods for producing
CN111936087A (en) 2018-03-30 2020-11-13 德普伊新特斯产品公司 Surface texture of three-dimensional porous structure for bone ingrowth and method of making
US11744695B2 (en) 2018-04-06 2023-09-05 Howmedica Osteonics Corp. Soft tissue attachment device
US10744003B2 (en) 2018-05-08 2020-08-18 Globus Medical, Inc. Intervertebral spinal implant
US10517739B2 (en) 2018-05-08 2019-12-31 Globus Medical, Inc. Intervertebral spinal implant
US10682238B2 (en) 2018-05-08 2020-06-16 Globus Medical, Inc. Intervertebral spinal implant
AU2019203591A1 (en) 2018-05-25 2019-12-12 Howmedica Osteonics Corp. Variable thickness femoral augments
KR102115229B1 (en) * 2018-06-20 2020-05-27 한국생산기술연구원 One-step manufacturing method of laminated molding porous component which has curved surface
KR102115225B1 (en) * 2018-06-20 2020-05-27 한국생산기술연구원 One-step manufacturing method of laminated molding porous component
US11065126B2 (en) 2018-08-09 2021-07-20 Stryker European Operations Holdings Llc Interbody implants and optimization features thereof
US10780498B2 (en) * 2018-08-22 2020-09-22 General Electric Company Porous tools and methods of making the same
WO2020061487A1 (en) 2018-09-20 2020-03-26 Amendia, Inc. d/b/a Spinal Elements Spinal implant device
AU2019355859A1 (en) 2018-10-01 2021-05-13 K2M, Inc. Graft scaffold
IT201800009553A1 (en) 2018-10-17 2020-04-17 Andrea Brovelli METHOD FOR MAKING SCREWS FOR INTRA-BONE FIXATIONS AND SCREWS OBTAINED BY THIS METHOD
US11534961B2 (en) 2018-11-09 2022-12-27 General Electric Company Melt pool monitoring system and method for detecting errors in a multi-laser additive manufacturing process
US11534257B2 (en) 2018-11-20 2022-12-27 Howmedica Osteonics Corp. Lattice impaction pad
US11717265B2 (en) 2018-11-30 2023-08-08 General Electric Company Methods and systems for an acoustic attenuating material
EP3666228A1 (en) 2018-12-14 2020-06-17 Howmedica Osteonics Corp. Augmented, just-in-time, patient-specific implant manufacture
CN111388156B (en) * 2018-12-29 2021-09-10 上海微创医疗器械(集团)有限公司 Biological coatings and implants
AU2020200077A1 (en) 2019-01-07 2020-07-23 Howmedica Osteonics Corp. Support frame
US11298244B2 (en) 2019-01-31 2022-04-12 K2M, Inc. Interbody implants and instrumentation
US11039931B2 (en) 2019-02-01 2021-06-22 Globus Medical, Inc. Intervertebral spinal implant
US11369419B2 (en) 2019-02-14 2022-06-28 Si-Bone Inc. Implants for spinal fixation and or fusion
AU2020223180A1 (en) 2019-02-14 2021-07-22 Si-Bone Inc. Implants for spinal fixation and or fusion
CN109811289B (en) * 2019-02-27 2020-11-06 中国科学院宁波工业技术研究院慈溪生物医学工程研究所 Surface modified titanium alloy and preparation method and application thereof
US20200281736A1 (en) 2019-03-04 2020-09-10 K2M, Inc. Intervertebral Implant Assembly and Instruments Therefor
WO2020254145A1 (en) * 2019-06-19 2020-12-24 The Swatch Group Research And Development Ltd Method for laser beam additive manufacturing of a machine part with technical and/or decorative function and machine part with technical and/or decorative function
AU2020210308A1 (en) 2019-08-01 2021-02-18 Howmedica Osteonics Corp. Multi-stage additive manufacturing process with inserts
CN110421172A (en) * 2019-08-27 2019-11-08 西安九洲生物材料有限公司 A method of medical porous tantalum part is prepared based on selective laser melting process
US11534307B2 (en) 2019-09-16 2022-12-27 K2M, Inc. 3D printed cervical standalone implant
EP4034044B1 (en) 2019-09-25 2023-08-16 DePuy Ireland Unlimited Company Three-dimensional porous structures for bone ingrowth
US11130131B2 (en) * 2019-09-26 2021-09-28 Lawrence Livermore National Security, Llc Lattice microfluidics
US11351034B2 (en) 2019-09-30 2022-06-07 DePuy Synthes Products, Inc. Patient specific femoral prosthesis
US11576787B2 (en) 2019-09-30 2023-02-14 DePuy Synthes Products, Inc. Patient specific femoral prosthesis
WO2021084484A2 (en) 2019-10-29 2021-05-06 Stryker European Operations Limited Surgical navigation tracker, system, and method
US11278416B2 (en) 2019-11-14 2022-03-22 Howmedica Osteonics Corp. Concentric keel TKA
EP4065015A4 (en) 2019-11-27 2024-01-03 Si Bone Inc Bone stabilizing implants and methods of placement across si joints
US11707361B2 (en) 2020-02-05 2023-07-25 K2M, Inc. Flexible interbody implant
US11806955B2 (en) 2020-02-26 2023-11-07 Depuy Ireland Unlimited Company Method for testing additively manufactured orthopaedic prosthetic components
AU2020437666A1 (en) 2020-03-25 2022-09-22 Encore Medical, Lp Dba Djo Surgical Joint implants having porous structures formed utilizing additive manufacturing and related systems and methods
AU2021202801A1 (en) 2020-05-07 2021-11-25 Howmedica Osteonics Corp. Stemless metaphyseal humeral implant
AU2021202888A1 (en) 2020-05-26 2021-12-16 Howmedica Osteonics Corp. Medial trochanteric plate fixation
AU2021203588A1 (en) 2020-06-03 2021-12-23 Howmedica Osteonics Corp. Intercalary endoprosthesis
US11745267B2 (en) * 2020-06-24 2023-09-05 National Cheng Kung University Additive manufacturing method
CN116438054A (en) 2020-09-11 2023-07-14 哈佩脊椎有限责任公司 Methods for forming implantable medical devices having varying compositions and porous structures
US20230404773A1 (en) 2020-10-02 2023-12-21 K2M, Inc. Spinal Interbody Implants
US20230380983A1 (en) 2020-10-14 2023-11-30 K2M, Inc. Spinal Interbody Implants
JP2022072723A (en) * 2020-10-30 2022-05-17 セイコーエプソン株式会社 Three-dimensional molding apparatus
BE1028795B1 (en) * 2020-11-12 2022-06-13 Umc Utrecht Holding Bv ACETABULAR IMPLANT AND PROCEDURE FOR DEFORMING THIS IMPLANT
EP4000555A1 (en) * 2020-11-13 2022-05-25 Common Sense Engineering and Consult An anatomical dental implant arranged to be implanted in a naturally occurring cavity of the jawbone
US11911284B2 (en) 2020-11-19 2024-02-27 Spinal Elements, Inc. Curved expandable interbody devices and deployment tools
AU2021397743A1 (en) 2020-12-09 2023-06-22 Si-Bone Inc. Sacro-iliac joint stabilizing implants and methods of implantation
EP4019164A1 (en) * 2020-12-22 2022-06-29 Siemens Energy Global GmbH & Co. KG Radiation strategy in additive production with pulsed irradiation
FR3118429B1 (en) * 2020-12-30 2023-11-24 Commissariat Energie Atomique Manufacturing process for a functional metal part delimiting a porous filtration media, using an additive manufacturing method, and functional part obtained
CN112974804A (en) * 2021-02-09 2021-06-18 广东省科学院新材料研究所 Structure-controllable porous material additive manufacturing method
CN112958906B (en) * 2021-03-25 2022-02-18 南京航空航天大学 Laser processing device and method suitable for AlN plate
CN113290242A (en) * 2021-04-26 2021-08-24 华中科技大学 Micro-nano porous functional device, additive manufacturing method and application thereof
CN113289057B (en) * 2021-05-19 2022-10-14 北京爱康宜诚医疗器材有限公司 Tantalum-coated orthopedic implant material, preparation method thereof and orthopedic implant
US20220387163A1 (en) 2021-06-08 2022-12-08 Howmedica Osteonics Corp. Additive Manufacturing of Porous Coatings Separate From Substrate
US20220410272A1 (en) 2021-06-29 2022-12-29 Howmedica Osteonics Corp. Supports For Cantilevered Elements During Additive Manufacturing And Methods Of Forming Such Supports
US20230028894A1 (en) * 2021-07-16 2023-01-26 Wisconsin Alumni Research Foundation Additive manufacturing with sealed pores
AU2022256159A1 (en) 2021-10-25 2023-05-11 Howmedica Osteonics Corp. Porous structure placement configured for manufacturing
CN113953527B (en) * 2021-10-29 2023-04-14 江苏科技大学 Self-adaptive layering method for laser deposition/ultrasonic treatment synchronous additive manufacturing
CN114226755B (en) * 2021-12-21 2023-04-07 清华大学 Metal-ceramic composite lattice manufacturing method and metal-ceramic composite lattice structure
EP4245242A1 (en) 2022-03-18 2023-09-20 Stryker Australia PTY LTD Bone resection scoring and planning
CN114632948B (en) * 2022-03-21 2022-11-15 中国海洋大学 Plasma and laser composite additive manufacturing method
CN114888304B (en) * 2022-05-11 2023-06-20 华东理工大学 Manufacturing method of composite porous structure liquid absorption core
AU2023202887A1 (en) 2022-05-12 2023-11-30 Howmedica Osteonics Corp. Fatigue resistant porous structure
CN115533122A (en) * 2022-12-01 2022-12-30 四川工程职业技术学院 Iron-based alloy body and forming method and application thereof

Citations (96)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US14403A (en) * 1856-03-11 Improved spirit blow-pipe
US3605123A (en) * 1969-04-29 1971-09-20 Melpar Inc Bone implant
US3806961A (en) * 1972-02-16 1974-04-30 Sulzer Ag Phosthetic patella implant
US3816855A (en) * 1971-06-01 1974-06-18 Nat Res Dev Knee joint prosthesis
US4085466A (en) * 1974-11-18 1978-04-25 National Research Development Corporation Prosthetic joint device
US4164794A (en) * 1977-04-14 1979-08-21 Union Carbide Corporation Prosthetic devices having coatings of selected porous bioengineering thermoplastics
US4202055A (en) * 1976-05-12 1980-05-13 Battelle-Institut E.V. Anchorage for highly stressed endoprostheses
US4218494A (en) * 1978-07-04 1980-08-19 Centro Richerche Fiat S.P.A. Process for coating a metallic surface with a wear-resistant material
US4305340A (en) * 1978-02-24 1981-12-15 Yuwa Sangyo Kabushiki Kaisha Method of forming a box-shaped structure from a foldable metal sheet
US4344193A (en) * 1980-11-28 1982-08-17 Kenny Charles H Meniscus prosthesis
US4385404A (en) * 1980-02-21 1983-05-31 J. & P. Coats, Limited Device and method for use in the treatment of damaged articular surfaces of human joints
US4502161A (en) * 1981-09-21 1985-03-05 Wall W H Prosthetic meniscus for the repair of joints
US4636219A (en) * 1985-12-05 1987-01-13 Techmedica, Inc. Prosthesis device fabrication
US4644942A (en) * 1981-07-27 1987-02-24 Battelle Development Corporation Production of porous coating on a prosthesis
US4673408A (en) * 1983-08-24 1987-06-16 Arthroplasty Research & Development (Pty) Ltd. Knee prosthesis
US4714474A (en) * 1986-05-12 1987-12-22 Dow Corning Wright Corporation Tibial knee joint prosthesis with removable articulating surface insert
US4714473A (en) * 1985-07-25 1987-12-22 Harrington Arthritis Research Center Knee prosthesis
US4719908A (en) * 1986-08-15 1988-01-19 Osteonics Corp. Method and apparatus for implanting a prosthetic device
US4863538A (en) * 1986-10-17 1989-09-05 Board Of Regents, The University Of Texas System Method and apparatus for producing parts by selective sintering
US4944817A (en) * 1986-10-17 1990-07-31 Board Of Regents, The University Of Texas System Multiple material systems for selective beam sintering
US4961154A (en) * 1986-06-03 1990-10-02 Scitex Corporation Ltd. Three dimensional modelling apparatus
US4969907A (en) * 1985-01-08 1990-11-13 Sulzer Brothers Limited Metal bone implant
US4990163A (en) * 1989-02-06 1991-02-05 Trustees Of The University Of Pennsylvania Method of depositing calcium phosphate cermamics for bone tissue calcification enhancement
US5004476A (en) * 1989-10-31 1991-04-02 Tulane University Porous coated total hip replacement system
US5017753A (en) * 1986-10-17 1991-05-21 Board Of Regents, The University Of Texas System Method and apparatus for producing parts by selective sintering
US5024670A (en) * 1989-10-02 1991-06-18 Depuy, Division Of Boehringer Mannheim Corporation Polymeric bearing component
US5031120A (en) * 1987-12-23 1991-07-09 Itzchak Pomerantz Three dimensional modelling apparatus
US5034186A (en) * 1985-11-20 1991-07-23 Permelec Electrode Ltd. Process for providing titanium composite having a porous surface
US5053090A (en) * 1989-09-05 1991-10-01 Board Of Regents, The University Of Texas System Selective laser sintering with assisted powder handling
US5067964A (en) * 1989-12-13 1991-11-26 Stryker Corporation Articular surface repair
US5076869A (en) * 1986-10-17 1991-12-31 Board Of Regents, The University Of Texas System Multiple material systems for selective beam sintering
US5080674A (en) * 1988-09-08 1992-01-14 Zimmer, Inc. Attachment mechanism for securing an additional portion to an implant
US5108432A (en) * 1990-06-24 1992-04-28 Pfizer Hospital Products Group, Inc. Porous fixation surface
US5147402A (en) * 1990-12-05 1992-09-15 Sulzer Brothers Limited Implant for ingrowth of osseous tissue
US5155324A (en) * 1986-10-17 1992-10-13 Deckard Carl R Method for selective laser sintering with layerwise cross-scanning
US5158574A (en) * 1987-07-20 1992-10-27 Regen Corporation Prosthetic meniscus
US5171282A (en) * 1990-01-12 1992-12-15 Societe Civile D'innovations Technologique Femoral member for knee prosthesis
US5176710A (en) * 1991-01-23 1993-01-05 Orthopaedic Research Institute Prosthesis with low stiffness factor
US5192328A (en) * 1989-09-29 1993-03-09 Winters Thomas F Knee joint replacement apparatus
US5219362A (en) * 1991-02-07 1993-06-15 Finsbury (Instruments) Limited Knee prosthesis
US5282870A (en) * 1992-01-14 1994-02-01 Sulzer Medizinaltechnik Ag Artificial knee joint
US5282861A (en) * 1992-03-11 1994-02-01 Ultramet Open cell tantalum structures for cancellous bone implants and cell and tissue receptors
US5287435A (en) * 1987-06-02 1994-02-15 Cubital Ltd. Three dimensional modeling
US5314478A (en) * 1991-03-29 1994-05-24 Kyocera Corporation Artificial bone connection prosthesis
US5323954A (en) * 1990-12-21 1994-06-28 Zimmer, Inc. Method of bonding titanium to a cobalt-based alloy substrate in an orthophedic implant device
US5358529A (en) * 1993-03-05 1994-10-25 Smith & Nephew Richards Inc. Plastic knee femoral implants
US5368602A (en) * 1993-02-11 1994-11-29 De La Torre; Roger A. Surgical mesh with semi-rigid border members
US5386500A (en) * 1987-06-02 1995-01-31 Cubital Ltd. Three dimensional modeling apparatus
US5398193A (en) * 1993-08-20 1995-03-14 Deangelis; Alfredo O. Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor
US5443510A (en) * 1993-04-06 1995-08-22 Zimmer, Inc. Porous coated implant and method of making same
US5443518A (en) * 1993-07-20 1995-08-22 Zimmer, Inc. Knee position indicator
US5490962A (en) * 1993-10-18 1996-02-13 Massachusetts Institute Of Technology Preparation of medical devices by solid free-form fabrication methods
US5496372A (en) * 1992-04-17 1996-03-05 Kyocera Corporation Hard tissue prosthesis including porous thin metal sheets
US5504300A (en) * 1994-04-18 1996-04-02 Zimmer, Inc. Orthopaedic implant and method of making same
US5514183A (en) * 1994-12-20 1996-05-07 Epstein; Norman Reduced friction prosthetic knee joint utilizing replaceable roller bearings
US5549700A (en) * 1993-09-07 1996-08-27 Ortho Development Corporation Segmented prosthetic articulation
US5571185A (en) * 1991-10-12 1996-11-05 Eska Implants Gmbh Process for the production of a bone implant and a bone implant produced thereby
US5571196A (en) * 1994-10-24 1996-11-05 Stein; Daniel Patello-femoral joint replacement device and method
US5609646A (en) * 1992-01-23 1997-03-11 Howmedica International Acetabular cup for a total hip prosthesis
US5616294A (en) * 1986-10-17 1997-04-01 Board Of Regents, The University Of Texas System Method for producing parts by infiltration of porous intermediate parts
US5640667A (en) * 1995-11-27 1997-06-17 Board Of Regents, The University Of Texas System Laser-directed fabrication of full-density metal articles using hot isostatic processing
US5648450A (en) * 1992-11-23 1997-07-15 Dtm Corporation Sinterable semi-crystalline powder and near-fully dense article formed therein
US5681354A (en) * 1996-02-20 1997-10-28 Board Of Regents, University Of Colorado Asymmetrical femoral component for knee prosthesis
US5702448A (en) * 1990-09-17 1997-12-30 Buechel; Frederick F. Prosthesis with biologically inert wear resistant surface
US5728162A (en) * 1993-01-28 1998-03-17 Board Of Regents Of University Of Colorado Asymmetric condylar and trochlear femoral knee component
US5735903A (en) * 1987-07-20 1998-04-07 Li; Shu-Tung Meniscal augmentation device
US5773789A (en) * 1994-04-18 1998-06-30 Bristol-Myers Squibb Company Method of making an orthopaedic implant having a porous metal pad
US5776201A (en) * 1995-10-02 1998-07-07 Johnson & Johnson Professional, Inc. Modular femoral trial system
US5782908A (en) * 1995-08-22 1998-07-21 Medtronic, Inc. Biocompatible medical article and method
US5795353A (en) * 1994-05-06 1998-08-18 Advanced Bio Surfaces, Inc. Joint resurfacing system
US5824098A (en) * 1994-10-24 1998-10-20 Stein; Daniel Patello-femoral joint replacement device and method
US5824102A (en) * 1992-06-19 1998-10-20 Buscayret; Christian Total knee prosthesis
US5879398A (en) * 1995-02-14 1999-03-09 Zimmer, Inc. Acetabular cup
US5879387A (en) * 1994-08-25 1999-03-09 Howmedica International Inc. Prosthetic bearing element and method of manufacture
US5928285A (en) * 1997-05-30 1999-07-27 Bristol-Myers Squibb Co. Orthopaedic implant having an articulating surface with a conforming and translational surface
US5973222A (en) * 1994-04-18 1999-10-26 Bristol-Myers Squibb Co. Orthopedic implant having a porous metal pad
US5989472A (en) * 1994-10-05 1999-11-23 Howmedica International, Inc. Method for making a reinforced orthopedic implant
US6046426A (en) * 1996-07-08 2000-04-04 Sandia Corporation Method and system for producing complex-shape objects
US6049054A (en) * 1994-04-18 2000-04-11 Bristol-Myers Squibb Company Method of making an orthopaedic implant having a porous metal pad
US6087553A (en) * 1996-02-26 2000-07-11 Implex Corporation Implantable metallic open-celled lattice/polyethylene composite material and devices
US6096043A (en) * 1998-12-18 2000-08-01 Depuy Orthopaedics, Inc. Epicondylar axis alignment-femoral positioning drill guide
US6132468A (en) * 1998-09-10 2000-10-17 Mansmann; Kevin A. Arthroscopic replacement of cartilage using flexible inflatable envelopes
US6139585A (en) * 1998-03-11 2000-10-31 Depuy Orthopaedics, Inc. Bioactive ceramic coating and method
US6190407B1 (en) * 1997-11-20 2001-02-20 St. Jude Medical, Inc. Medical article with adhered antimicrobial metal
US6206927B1 (en) * 1999-04-02 2001-03-27 Barry M. Fell Surgically implantable knee prothesis
US6206924B1 (en) * 1999-10-20 2001-03-27 Interpore Cross Internat Three-dimensional geometric bio-compatible porous engineered structure for use as a bone mass replacement or fusion augmentation device
US6215093B1 (en) * 1996-12-02 2001-04-10 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Selective laser sintering at melting temperature
US6248131B1 (en) * 1994-05-06 2001-06-19 Advanced Bio Surfaces, Inc. Articulating joint repair
US6251143B1 (en) * 1999-06-04 2001-06-26 Depuy Orthopaedics, Inc. Cartilage repair unit
US6261322B1 (en) * 1998-05-14 2001-07-17 Hayes Medical, Inc. Implant with composite coating
US20010014403A1 (en) * 1997-08-12 2001-08-16 Lawrence Evans Brown Method and apparatus for making components by direct laser processing
US6280478B1 (en) * 1997-03-04 2001-08-28 Implico B.V. Artefact suitable for use as a bone implant
US6283997B1 (en) * 1998-11-13 2001-09-04 The Trustees Of Princeton University Controlled architecture ceramic composites by stereolithography
US6299645B1 (en) * 1999-07-23 2001-10-09 William S. Ogden Dove tail total knee replacement unicompartmental
US6371958B1 (en) * 2000-03-02 2002-04-16 Ethicon, Inc. Scaffold fixation device for use in articular cartilage repair
US6395327B1 (en) * 1999-03-12 2002-05-28 Zimmer, Inc. Enhanced fatigue strength orthopaedic implant with porous coating and method of making same

Family Cites Families (305)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US222687A (en) * 1879-12-16 Improvement in combined pencil and line-measurer
US2222687A (en) 1936-05-08 1940-11-26 Maiden Form Brassiere Company Strap construction
US2373769A (en) 1942-08-17 1945-04-17 Claude W Macy Tire repairing device
US3520099A (en) * 1968-09-16 1970-07-14 Mastic Corp Interlocking building siding unit
US3556918A (en) * 1968-12-03 1971-01-19 Jerome H Lemelson Composite reinforced plastic foam sheet
US3826054A (en) * 1972-05-15 1974-07-30 B Culpepper Building insulation and sheathing
FR2214460B1 (en) 1973-01-18 1976-05-14 Ceraver
US3906550A (en) 1973-12-27 1975-09-23 William Rostoker Prosthetic device having a porous fiber metal structure
US4117302A (en) 1974-03-04 1978-09-26 Caterpillar Tractor Co. Method for fusibly bonding a coating material to a metal article
US4073999A (en) 1975-05-09 1978-02-14 Minnesota Mining And Manufacturing Company Porous ceramic or metallic coatings and articles
US4047349A (en) 1976-05-14 1977-09-13 Johns-Manville Corporation Sheet material attaching device and wall arrangement using this device
US4259072A (en) 1977-04-04 1981-03-31 Kyoto Ceramic Co., Ltd. Ceramic endosseous implant
US4154040A (en) * 1978-02-24 1979-05-15 Pace Thomas G Building siding and beveled backer panel assembly and method
US4247508B1 (en) 1979-12-03 1996-10-01 Dtm Corp Molding process
US4479271A (en) 1981-10-26 1984-10-30 Zimmer, Inc. Prosthetic device adapted to promote bone/tissue ingrowth
JPS58132068A (en) * 1982-01-30 1983-08-06 Nitto Electric Ind Co Ltd Reinforcing adhesive sheet
CA1227002A (en) 1982-02-18 1987-09-22 Robert V. Kenna Bone prosthesis with porous coating
US4542539A (en) 1982-03-12 1985-09-24 Artech Corp. Surgical implant having a graded porous coating
US4474861A (en) 1983-03-09 1984-10-02 Smith International, Inc. Composite bearing structure of alternating hard and soft metal, and process for making the same
US4659331A (en) 1983-11-28 1987-04-21 Regents Of University Of Michigan Prosthesis interface surface and method of implanting
US4543158A (en) 1984-04-02 1985-09-24 Gaf Corporation Sheet type felt
US4513045A (en) * 1984-04-02 1985-04-23 Gaf Corporation Sheet type felt
US4673409A (en) 1984-04-25 1987-06-16 Minnesota Mining And Manufacturing Company Implant with attachment surface
CA1264674A (en) * 1984-10-17 1990-01-23 Paul Ducheyne Porous flexible metal fiber material for surgical implantation
CH665348A5 (en) 1985-01-09 1988-05-13 Sulzer Ag IMPLANTS.
US4969302A (en) 1985-01-15 1990-11-13 Abitibi-Price Corporation Siding panels
CH665770A5 (en) 1985-01-25 1988-06-15 Sulzer Ag PLASTIC BONE IMPLANT.
US5002572A (en) 1986-09-11 1991-03-26 Picha George J Biological implant with textured surface
US4766029A (en) 1987-01-23 1988-08-23 Kimberly-Clark Corporation Semi-permeable nonwoven laminate
US20020102674A1 (en) 1987-05-20 2002-08-01 David M Anderson Stabilized microporous materials
US4837067A (en) 1987-06-08 1989-06-06 Minnesota Mining And Manufacturing Company Nonwoven thermal insulating batts
US5306311A (en) 1987-07-20 1994-04-26 Regen Corporation Prosthetic articular cartilage
CH672985A5 (en) 1987-11-11 1990-01-31 Sulzer Ag
US4944756A (en) 1988-02-03 1990-07-31 Pfizer Hospital Products Group Prosthetic knee joint with improved patellar component tracking
JP2829318B2 (en) 1988-06-10 1998-11-25 春幸 川原 Frameless, coreless porous endosseous implant
US5486599A (en) 1989-03-29 1996-01-23 The Board Of Trustees Of The Leland Stanford Junior University Construction and use of synthetic constructs encoding syndecan
JPH0813519B2 (en) 1989-03-29 1996-02-14 東レ株式会社 Glass fiber mat Insulation lining Metal origami shingles
EP0425714A1 (en) 1989-10-28 1991-05-08 Metalpraecis Berchem + Schaberg Gesellschaft Für Metallformgebung Mbh Process for manufacturing an implantable joint prosthesis
GB8925380D0 (en) 1989-11-09 1989-12-28 Leonard Ian Producing prostheses
US4997445A (en) 1989-12-08 1991-03-05 Zimmer, Inc. Metal-backed prosthetic implant with enhanced bonding of polyethylene portion to metal base
JPH041794A (en) 1990-04-19 1992-01-07 Sakurai Kk Adhesive sheet for display
US5122116A (en) 1990-04-24 1992-06-16 Science Incorporated Closed drug delivery system
JPH0441794A (en) 1990-06-01 1992-02-12 Mitsubishi Paper Mills Ltd Fiber sheet and its complex sheet
US5108441A (en) 1990-07-17 1992-04-28 Mcdowell Charles L Method of regenerating joint articular cartilage
US5090174A (en) * 1990-09-26 1992-02-25 Fragale Anthony J Siding system including siding trim pieces and method of siding a structure using same
US5274565A (en) 1990-10-03 1993-12-28 Board Of Regents, The University Of Texas System Process for making custom joint replacements
US5258098A (en) 1991-06-17 1993-11-02 Cycam, Inc. Method of production of a surface adapted to promote adhesion
DE59108588D1 (en) 1991-08-07 1997-04-10 Oscobal Ag Endoprosthesis with a metal wire
US5356433A (en) 1991-08-13 1994-10-18 Cordis Corporation Biocompatible metal surfaces
DE4205969C2 (en) 1992-02-27 1994-07-07 Merck Patent Gmbh Process for the production of moldings with a predetermined pore structure
CA2075553A1 (en) * 1992-08-07 1994-02-08 George Zafir Insulated panel
US5510066A (en) 1992-08-14 1996-04-23 Guild Associates, Inc. Method for free-formation of a free-standing, three-dimensional body
US5370692A (en) 1992-08-14 1994-12-06 Guild Associates, Inc. Rapid, customized bone prosthesis
US5527877A (en) 1992-11-23 1996-06-18 Dtm Corporation Sinterable semi-crystalline powder and near-fully dense article formed therewith
US5336518A (en) 1992-12-11 1994-08-09 Cordis Corporation Treatment of metallic surfaces using radiofrequency plasma deposition and chemical attachment of bioactive agents
US5352405A (en) 1992-12-18 1994-10-04 Dtm Corporation Thermal control of selective laser sintering via control of the laser scan
US5380328A (en) * 1993-08-09 1995-01-10 Timesh, Inc. Composite perforated implant structures
DE69432023T2 (en) 1993-09-10 2003-10-23 Univ Queensland Santa Lucia STEREOLITHOGRAPHIC ANATOMIC MODELING PROCESS
US5518680A (en) * 1993-10-18 1996-05-21 Massachusetts Institute Of Technology Tissue regeneration matrices by solid free form fabrication techniques
DE4341367C1 (en) 1993-12-04 1995-06-14 Harald Dr Med Dr Med Eufinger Process for the production of endoprostheses
US6415574B2 (en) * 1993-12-22 2002-07-09 Certainteed Corp. Reinforced exterior siding
US5461839A (en) * 1993-12-22 1995-10-31 Certainteed Corporation Reinforced exterior siding
US5665118A (en) 1994-02-18 1997-09-09 Johnson & Johnson Professional, Inc. Bone prostheses with direct cast macrotextured surface regions and method for manufacturing the same
BE1008372A3 (en) 1994-04-19 1996-04-02 Materialise Nv METHOD FOR MANUFACTURING A perfected MEDICAL MODEL BASED ON DIGITAL IMAGE INFORMATION OF A BODY.
IL109344A (en) 1994-04-19 1998-02-22 Mendes David Prosthetic patella implant of the knee joint
US5857303A (en) * 1994-05-13 1999-01-12 Certainteed Corporation Apparatus and method of applying building panels to surfaces
US5729946A (en) * 1994-05-13 1998-03-24 Certainteed Corporation Apparatus and method of applying building panels to surfaces
US5639402A (en) 1994-08-08 1997-06-17 Barlow; Joel W. Method for fabricating artificial bone implant green parts
US6290726B1 (en) 2000-01-30 2001-09-18 Diamicron, Inc. Prosthetic hip joint having sintered polycrystalline diamond compact articulation surfaces
US7494507B2 (en) 2000-01-30 2009-02-24 Diamicron, Inc. Articulating diamond-surfaced spinal implants
US5632745A (en) 1995-02-07 1997-05-27 R&D Biologicals, Inc. Surgical implantation of cartilage repair unit
US5769899A (en) 1994-08-12 1998-06-23 Matrix Biotechnologies, Inc. Cartilage repair unit
DE19502733A1 (en) 1994-09-20 1996-03-21 Gefinex Jackon Gmbh Tiling panel for interiors
US5716358A (en) 1994-12-02 1998-02-10 Johnson & Johnson Professional, Inc. Directional bone fixation device
US5489306A (en) 1995-01-03 1996-02-06 Gorski; Jerrold M. Graduated porosity implant for fibro-osseous integration
US6051751A (en) 1995-01-20 2000-04-18 Spire Corporation Arthroplasty process for securely anchoring prostheses to bone, and arthroplasty products therefor
US5749874A (en) 1995-02-07 1998-05-12 Matrix Biotechnologies, Inc. Cartilage repair unit and method of assembling same
DE19511772C2 (en) 1995-03-30 1997-09-04 Eos Electro Optical Syst Device and method for producing a three-dimensional object
US6149688A (en) 1995-06-07 2000-11-21 Surgical Dynamics, Inc. Artificial bone graft implant
US6209621B1 (en) 1995-07-07 2001-04-03 Depuy Orthopaedics, Inc. Implantable prostheses with metallic porous bead preforms applied during casting and method of forming the same
EP0761242A1 (en) 1995-08-21 1997-03-12 Bristol-Myers Squibb Company Orthopaedic implant with bearing surface
US6149689A (en) 1995-11-22 2000-11-21 Eska Implants Gmbh & Co. Implant as bone replacement
US5769092A (en) 1996-02-22 1998-06-23 Integrated Surgical Systems, Inc. Computer-aided system for revision total hip replacement surgery
US6143948A (en) 1996-05-10 2000-11-07 Isotis B.V. Device for incorporation and release of biologically active agents
AU2759397A (en) 1996-05-28 1998-01-05 1218122 Ontario Inc. Resorbable implant biomaterial made of condensed calcium phosphate particles
US5811151A (en) 1996-05-31 1998-09-22 Medtronic, Inc. Method of modifying the surface of a medical device
US6476343B2 (en) 1996-07-08 2002-11-05 Sandia Corporation Energy-beam-driven rapid fabrication system
US6013855A (en) 1996-08-06 2000-01-11 United States Surgical Grafting of biocompatible hydrophilic polymers onto inorganic and metal surfaces
US5989269A (en) 1996-08-30 1999-11-23 Vts Holdings L.L.C. Method, instruments and kit for autologous transplantation
US7332537B2 (en) 1996-09-04 2008-02-19 Z Corporation Three dimensional printing material system and method
GB2318058B (en) 1996-09-25 2001-03-21 Ninian Spenceley Peckitt Improvements relating to prosthetic implants
US6530951B1 (en) * 1996-10-24 2003-03-11 Cook Incorporated Silver implantable medical device
US6128866A (en) 1996-11-08 2000-10-10 Wearne; John R. Identifying prefabricated exterior siding and related trim items
US6261493B1 (en) * 1997-03-20 2001-07-17 Therics, Inc. Fabrication of tissue products with additives by casting or molding using a mold formed by solid free-form methods
US6240616B1 (en) 1997-04-15 2001-06-05 Advanced Cardiovascular Systems, Inc. Method of manufacturing a medicated porous metal prosthesis
BE1011244A3 (en) 1997-06-30 1999-06-01 Bekaert Sa Nv LAYERED TUBULAR METAL STRUCTURE.
US6045581A (en) 1997-12-12 2000-04-04 Sulzer Orthopedics Inc. Implantable prosthesis having textured bearing surfaces
US6208959B1 (en) * 1997-12-15 2001-03-27 Telefonaktibolaget Lm Ericsson (Publ) Mapping of digital data symbols onto one or more formant frequencies for transmission over a coded voice channel
WO1999033641A1 (en) 1997-12-24 1999-07-08 Molecular Geodesics, Inc. Foam scaffold materials
US6171340B1 (en) 1998-02-27 2001-01-09 Mcdowell Charles L. Method and device for regenerating cartilage in articulating joints
JPH11287020A (en) 1998-04-03 1999-10-19 Ig Tech Res Inc Soundproof exterior finish material
US20010008674A1 (en) 1998-05-23 2001-07-19 Ralph Smith Underlayment mat employed with a single ply roofing system
JPH11348045A (en) 1998-06-10 1999-12-21 Matsushita Electric Ind Co Ltd Metal mold
US6774071B2 (en) * 1998-09-08 2004-08-10 Building Materials Investment Corporation Foamed facer and insulation boards made therefrom
US6350284B1 (en) 1998-09-14 2002-02-26 Bionx Implants, Oy Bioabsorbable, layered composite material for guided bone tissue regeneration
AU768641B2 (en) 1998-10-12 2003-12-18 Massachusetts Institute Of Technology Composites for tissue regeneration and methods of manufacture thereof
US7343960B1 (en) 1998-11-20 2008-03-18 Rolls-Royce Corporation Method and apparatus for production of a cast component
DE19901643A1 (en) * 1999-01-19 2000-07-20 Herbst Bremer Goldschlaegerei Process for the production of dentures and dental auxiliary parts
US20020187458A1 (en) 1999-01-19 2002-12-12 Bego Bremer Goldschlagerei Wilh. Herbst Gmbh & Co. Method for producing tooth replacements and auxiliary dental parts
RU2218242C2 (en) 1999-02-11 2003-12-10 Физический институт им. П.Н. Лебедева РАН Method for making medical implants from biologically compatible materials
US6206883B1 (en) * 1999-03-05 2001-03-27 Stryker Technologies Corporation Bioabsorbable materials and medical devices made therefrom
US6558421B1 (en) * 2000-09-19 2003-05-06 Barry M. Fell Surgically implantable knee prosthesis
US7341602B2 (en) * 1999-05-10 2008-03-11 Fell Barry M Proportioned surgically implantable knee prosthesis
US6582715B1 (en) 1999-04-27 2003-06-24 Agion Technologies, Inc. Antimicrobial orthopedic implants
US6370382B1 (en) * 1999-04-27 2002-04-09 Qualcomm Incorporated System and method for reducing wireless telecommunications network resources required to successfully route calls to a wireline network
US7338524B2 (en) 1999-05-10 2008-03-04 Fell Barry M Surgically implantable knee prosthesis
US6855165B2 (en) * 1999-05-10 2005-02-15 Barry M. Fell Surgically implantable knee prosthesis having enlarged femoral surface
US6893463B2 (en) * 1999-05-10 2005-05-17 Barry M. Fell Surgically implantable knee prosthesis having two-piece keyed components
US7491235B2 (en) 1999-05-10 2009-02-17 Fell Barry M Surgically implantable knee prosthesis
US6966928B2 (en) * 1999-05-10 2005-11-22 Fell Barry M Surgically implantable knee prosthesis having keels
US7297161B2 (en) 1999-05-10 2007-11-20 Fell Barry M Surgically implantable knee prosthesis
US6923831B2 (en) * 1999-05-10 2005-08-02 Barry M. Fell Surgically implantable knee prosthesis having attachment apertures
US6911044B2 (en) * 1999-05-10 2005-06-28 Barry M. Fell Surgically implantable knee prosthesis having medially shifted tibial surface
US6866684B2 (en) * 1999-05-10 2005-03-15 Barry M. Fell Surgically implantable knee prosthesis having different tibial and femoral surface profiles
US20050033424A1 (en) * 1999-05-10 2005-02-10 Fell Barry M. Surgically implantable knee prosthesis
US6520996B1 (en) * 1999-06-04 2003-02-18 Depuy Acromed, Incorporated Orthopedic implant
US6811744B2 (en) * 1999-07-07 2004-11-02 Optomec Design Company Forming structures from CAD solid models
US6702848B1 (en) 1999-07-20 2004-03-09 Peter Paul Zilla Foam-type vascular prosthesis with well-defined anclio-permissive open porosity
US6368354B2 (en) 1999-10-07 2002-04-09 Exactech, Inc. Acetabular bearing assembly for total hip joints
JP2003512110A (en) 1999-10-15 2003-04-02 マウント・シナイ・ホスピタル Synthetic substrate for tissue formation
JP2003518193A (en) 1999-11-16 2003-06-03 トリトン・システムズ・インコーポレイテツド Laser processing of discontinuous reinforced metal matrix composites
FR2801193B1 (en) 1999-11-19 2002-02-15 Proconcept DOUBLE MOBILITY EXPANDABLE COTYLOIDAL PROSTHESIS
US20040009228A1 (en) 1999-11-30 2004-01-15 Pertti Tormala Bioabsorbable drug delivery system for local treatment and prevention of infections
US7115143B1 (en) 1999-12-08 2006-10-03 Sdgi Holdings, Inc. Orthopedic implant surface configuration
US20050203630A1 (en) 2000-01-30 2005-09-15 Pope Bill J. Prosthetic knee joint having at least one diamond articulation surface
KR100358192B1 (en) 2000-02-16 2002-10-25 한국과학기술원 Jacket for cementless artificial joint and the artificial joint with it
US6551608B2 (en) 2000-03-06 2003-04-22 Porex Technologies Corporation Porous plastic media with antiviral or antimicrobial properties and processes for making the same
US6626945B2 (en) 2000-03-14 2003-09-30 Chondrosite, Llc Cartilage repair plug
US6632246B1 (en) 2000-03-14 2003-10-14 Chondrosite, Llc Cartilage repair plug
US6712856B1 (en) * 2000-03-17 2004-03-30 Kinamed, Inc. Custom replacement device for resurfacing a femur and method of making the same
EP1312025A2 (en) * 2000-04-05 2003-05-21 Therics, Inc. System and method for rapidly customizing a design and remotely manufacturing biomedical devices using a computer system
US6772026B2 (en) 2000-04-05 2004-08-03 Therics, Inc. System and method for rapidly customizing design, manufacture and/or selection of biomedical devices
ITVI20000025U1 (en) * 2000-04-07 2001-10-07 Tecres Spa TEMPORARY SPACER DEVICE FOR SURGICAL TREATMENT OF THE KNEE
TW462510U (en) 2000-04-24 2001-11-01 Delta Electronics Inc Hanged-type eccentric fan
JP4465802B2 (en) 2000-04-25 2010-05-26 日東紡績株式会社 Siding panel and outer wall panel using the same
AU2001259327B2 (en) 2000-05-01 2005-02-17 Arthrosurface, Inc. System and method for joint resurface repair
US7618462B2 (en) 2000-05-01 2009-11-17 Arthrosurface Incorporated System and method for joint resurface repair
US6610067B2 (en) 2000-05-01 2003-08-26 Arthrosurface, Incorporated System and method for joint resurface repair
US7163541B2 (en) 2002-12-03 2007-01-16 Arthrosurface Incorporated Tibial resurfacing system
US20040230315A1 (en) 2000-05-01 2004-11-18 Ek Steven W. Articular surface implant
US6679917B2 (en) 2000-05-01 2004-01-20 Arthrosurface, Incorporated System and method for joint resurface repair
WO2001092001A1 (en) 2000-05-26 2001-12-06 University Of Virginia Patent Foundation Multifunctional periodic cellular solids and the method of making thereof
US6676892B2 (en) * 2000-06-01 2004-01-13 Board Of Regents, University Texas System Direct selective laser sintering of metals
US20020130112A1 (en) 2000-06-05 2002-09-19 Mark Manasas Orthopedic implant and method of making metal articles
JP3679315B2 (en) * 2000-07-19 2005-08-03 経憲 武井 Knee prosthesis
JP2004521666A (en) 2000-08-28 2004-07-22 アドバンスト バイオ サーフェイシズ,インコーポレイティド Methods and systems for enhancing mammalian joints
US20020062154A1 (en) 2000-09-22 2002-05-23 Ayers Reed A. Non-uniform porosity tissue implant
DE10057675C2 (en) * 2000-11-21 2003-02-13 Andrej Nowakowski Knee endoprosthesis
US6494914B2 (en) 2000-12-05 2002-12-17 Biomet, Inc. Unicondylar femoral prosthesis and instruments
US6599323B2 (en) 2000-12-21 2003-07-29 Ethicon, Inc. Reinforced tissue implants and methods of manufacture and use
ATE387161T1 (en) 2001-01-25 2008-03-15 Smith & Nephew Inc RETAINING DEVICE FOR HOLDING A PROSTHETIC COMPONENT
US6599322B1 (en) 2001-01-25 2003-07-29 Tecomet, Inc. Method for producing undercut micro recesses in a surface, a surgical implant made thereby, and method for fixing an implant to bone
US9050192B2 (en) 2001-02-05 2015-06-09 Formae, Inc. Cartilage repair implant with soft bearing surface and flexible anchoring device
US6863689B2 (en) 2001-07-16 2005-03-08 Spinecore, Inc. Intervertebral spacer having a flexible wire mesh vertebral body contact element
EP1362129A1 (en) 2001-02-19 2003-11-19 IsoTis N.V. Porous metals and metal coatings for implants
US7597715B2 (en) 2005-04-21 2009-10-06 Biomet Manufacturing Corp. Method and apparatus for use of porous implants
US6743232B2 (en) 2001-02-26 2004-06-01 David W. Overaker Tissue scaffold anchor for cartilage repair
EP1247537A1 (en) 2001-04-04 2002-10-09 Isotis B.V. Coating for medical devices
EP1379287A1 (en) 2001-04-12 2004-01-14 Therics, Inc. Method and apparatus for engineered regenerative biostructures
US6699252B2 (en) * 2001-04-17 2004-03-02 Regeneration Technologies, Inc. Methods and instruments for improved meniscus transplantation
WO2002085246A2 (en) 2001-04-19 2002-10-31 Case Western Reserve University Fabrication of a polymeric prosthetic implant
US6589283B1 (en) 2001-05-15 2003-07-08 Biomet, Inc. Elongated femoral component
US6482209B1 (en) 2001-06-14 2002-11-19 Gerard A. Engh Apparatus and method for sculpting the surface of a joint
US7174282B2 (en) 2001-06-22 2007-02-06 Scott J Hollister Design methodology for tissue engineering scaffolds and biomaterial implants
JP3646162B2 (en) 2001-07-04 2005-05-11 独立行政法人産業技術総合研究所 Transplant for cartilage tissue regeneration
WO2003013338A2 (en) * 2001-08-07 2003-02-20 Depuy Orthopaedic, Inc Patello-femoral joint arthroplasty
GB0119652D0 (en) 2001-08-11 2001-10-03 Stanmore Implants Worldwide Surgical implant
US6850125B2 (en) * 2001-08-15 2005-02-01 Gallitzin Allegheny Llc Systems and methods for self-calibration
US6749639B2 (en) * 2001-08-27 2004-06-15 Mayo Foundation For Medical Education And Research Coated prosthetic implant
US6682567B1 (en) 2001-09-19 2004-01-27 Biomet, Inc. Method and apparatus for providing a shell component incorporating a porous ingrowth material and liner
US20030060113A1 (en) 2001-09-20 2003-03-27 Christie Peter A. Thermo formable acoustical panel
JP4330991B2 (en) * 2001-10-01 2009-09-16 スキャンディウス・バイオメディカル・インコーポレーテッド Apparatus and method for repairing articular cartilage defects
US6686437B2 (en) * 2001-10-23 2004-02-03 M.M.A. Tech Ltd. Medical implants made of wear-resistant, high-performance polyimides, process of making same and medical use of same
FR2831426B1 (en) 2001-10-30 2004-07-16 Tornier Sa JOINT IMPLANT AND KNEE PROSTHESIS INCORPORATING SUCH AN IMPLANT
US6709462B2 (en) * 2002-01-11 2004-03-23 Mayo Foundation For Medical Education And Research Acetabular shell with screw access channels
US6966932B1 (en) 2002-02-05 2005-11-22 Biomet, Inc. Composite acetabular component
US7458991B2 (en) 2002-02-08 2008-12-02 Howmedica Osteonics Corp. Porous metallic scaffold for tissue ingrowth
JP3781186B2 (en) 2002-02-13 2006-05-31 徹 勝呂 Knee prosthesis
US6740186B2 (en) 2002-02-20 2004-05-25 Zimmer Technology, Inc. Method of making an orthopeadic implant having a porous metal surface
EP1476097A4 (en) 2002-02-20 2010-12-08 Zimmer Inc Knee arthroplasty prosthesis and method
GB0204381D0 (en) * 2002-02-26 2002-04-10 Mcminn Derek J W Knee prosthesis
US20030220696A1 (en) 2002-05-23 2003-11-27 Levine David Jerome Implantable porous metal
US7918382B2 (en) 2002-06-18 2011-04-05 Zimmer Technology, Inc. Method for attaching a porous metal layer to a metal substrate
US20040006393A1 (en) 2002-07-03 2004-01-08 Brian Burkinshaw Implantable prosthetic knee for lateral compartment
AU2003249310A1 (en) * 2002-07-17 2004-02-02 Proxy Biomedical Limited Soft tissue implants and methods for making same
US20050103765A1 (en) * 2002-07-31 2005-05-19 Akira Kawasaki Method and device for forming a body having a three-dimensional structure
US7618907B2 (en) * 2002-08-02 2009-11-17 Owens Corning Intellectual Capital, Llc Low porosity facings for acoustic applications
DE60322066D1 (en) 2002-08-15 2008-08-21 Hfsc Co BAND DISC IMPLANT
US7008226B2 (en) 2002-08-23 2006-03-07 Woodwelding Ag Implant, in particular a dental implant
US20060106419A1 (en) 2002-08-23 2006-05-18 Peter Gingras Three dimensional implant
US20040054416A1 (en) * 2002-09-12 2004-03-18 Joe Wyss Posterior stabilized knee with varus-valgus constraint
GB2393625C (en) 2002-09-26 2004-08-18 Meridian Tech Ltd Orthopaedic surgery planning
US7637942B2 (en) 2002-11-05 2009-12-29 Merit Medical Systems, Inc. Coated stent with geometry determinated functionality and method of making the same
EP1418013B1 (en) 2002-11-08 2005-01-19 Howmedica Osteonics Corp. Laser-produced porous surface
US20060147332A1 (en) 2004-12-30 2006-07-06 Howmedica Osteonics Corp. Laser-produced porous structure
US20050070989A1 (en) 2002-11-13 2005-03-31 Whye-Kei Lye Medical devices having porous layers and methods for making the same
US6770099B2 (en) * 2002-11-19 2004-08-03 Zimmer Technology, Inc. Femoral prosthesis
JP3927487B2 (en) 2002-12-02 2007-06-06 株式会社大野興業 Manufacturing method of artificial bone model
US6878427B2 (en) * 2002-12-20 2005-04-12 Kimberly Clark Worldwide, Inc. Encased insulation article
US7160330B2 (en) 2003-01-21 2007-01-09 Howmedica Osteonics Corp. Emulating natural knee kinematics in a knee prosthesis
US6994730B2 (en) 2003-01-31 2006-02-07 Howmedica Osteonics Corp. Meniscal and tibial implants
US6916341B2 (en) 2003-02-20 2005-07-12 Lindsey R. Rolston Device and method for bicompartmental arthroplasty
US20040167632A1 (en) 2003-02-24 2004-08-26 Depuy Products, Inc. Metallic implants having roughened surfaces and methods for producing the same
JP4239652B2 (en) 2003-03-31 2009-03-18 パナソニック電工株式会社 Surface finishing method for metal powder sintered parts
US7364590B2 (en) 2003-04-08 2008-04-29 Thomas Siebel Anatomical knee prosthesis
BRPI0409487A (en) 2003-04-16 2006-05-02 Porex Surgical Inc surgical implant, process for its preparation and method of reconstruction of a bone defect
US6993406B1 (en) 2003-04-24 2006-01-31 Sandia Corporation Method for making a bio-compatible scaffold
BRPI0410324A (en) * 2003-05-15 2006-05-23 Biomerix Corp implantable device, elastomeric matrix production lyophilization processes having a cross-linked structure, polymerization for cross-linked elastomeric matrix preparation and cross-linked composite elastomeric implant preparation, and method for treating an orthopedic disorder
AU2004238026A1 (en) 2003-05-16 2004-11-25 Cinvention Ag Medical implants comprising biocompatible coatings
WO2004110309A2 (en) 2003-06-11 2004-12-23 Case Western Reserve University Computer-aided-design of skeletal implants
US20040262809A1 (en) 2003-06-30 2004-12-30 Smith Todd S. Crosslinked polymeric composite for orthopaedic implants
EP1648348B1 (en) 2003-07-24 2015-06-17 Tecomet Inc. Assembled non-random foams
US20050085922A1 (en) 2003-10-17 2005-04-21 Shappley Ben R. Shaped filler for implantation into a bone void and methods of manufacture and use thereof
GB0325647D0 (en) 2003-11-03 2003-12-10 Finsbury Dev Ltd Prosthetic implant
PL1687133T3 (en) 2003-11-04 2011-05-31 Porex Corp Composite porous materials and methods of making and using the same
US20050100578A1 (en) * 2003-11-06 2005-05-12 Schmid Steven R. Bone and tissue scaffolding and method for producing same
US7001672B2 (en) 2003-12-03 2006-02-21 Medicine Lodge, Inc. Laser based metal deposition of implant structures
US7294149B2 (en) 2003-12-05 2007-11-13 Howmedica Osteonics Corp. Orthopedic implant with angled pegs
CN1972646B (en) 2004-01-12 2010-05-26 德普伊产品公司 Systems and methods for compartmental replacement in a knee
WO2005069957A2 (en) 2004-01-20 2005-08-04 Alexander Michalow Unicondylar knee implant
US7189263B2 (en) 2004-02-03 2007-03-13 Vita Special Purpose Corporation Biocompatible bone graft material
US7442196B2 (en) 2004-02-06 2008-10-28 Synvasive Technology, Inc. Dynamic knee balancer
US7168283B2 (en) 2004-02-09 2007-01-30 Ast Acquisitions, Llc Cobalt chrome forging of femoral knee implants and other components
DE102004009126A1 (en) 2004-02-25 2005-09-22 Bego Medical Ag Method and device for generating control data sets for the production of products by free-form sintering or melting and device for this production
CA2557436A1 (en) 2004-03-05 2005-09-29 The Trustees Of Columbia University In The City Of New York Polymer-ceramic-hydrogel composite scaffold for osteochondral repair
GB0405680D0 (en) 2004-03-13 2004-04-21 Accentus Plc Metal implants
US7465318B2 (en) 2004-04-15 2008-12-16 Soteira, Inc. Cement-directing orthopedic implants
US7981942B2 (en) 2004-06-07 2011-07-19 Ticona Llc Polyethylene molding powder and porous articles made therefrom
WO2006007861A1 (en) 2004-07-16 2006-01-26 Universität Duisburg-Essen Implant
JP5154930B2 (en) 2004-07-19 2013-02-27 スミス アンド ネフュー インコーポレーテッド Pulse electric current sintering method of the surface of a medical implant and the medical implant
US20060036251A1 (en) 2004-08-09 2006-02-16 Reiley Mark A Systems and methods for the fixation or fusion of bone
US7351423B2 (en) 2004-09-01 2008-04-01 Depuy Spine, Inc. Musculo-skeletal implant having a bioactive gradient
GB0419961D0 (en) 2004-09-08 2004-10-13 Sudmann Einar Prosthetic element
GB0422666D0 (en) 2004-10-12 2004-11-10 Benoist Girard Sas Prosthetic acetabular cups
WO2006053291A2 (en) 2004-11-09 2006-05-18 Proxy Biomedical Limited Tissue scaffold
US20060254200A1 (en) 2004-11-19 2006-11-16 The Trustees Of Columbia University In The City Of New York Systems and methods for construction of space-truss structures
SG123615A1 (en) 2004-12-10 2006-07-26 Nanyang Polytechnic Method for designing 3-dimensional porous tissue engineering scaffold
US7879275B2 (en) 2004-12-30 2011-02-01 Depuy Products, Inc. Orthopaedic bearing and method for making the same
US7718109B2 (en) 2005-02-14 2010-05-18 Mayo Foundation For Medical Education And Research Tissue support structure
US8066778B2 (en) 2005-04-21 2011-11-29 Biomet Manufacturing Corp. Porous metal cup with cobalt bearing surface
US8292967B2 (en) 2005-04-21 2012-10-23 Biomet Manufacturing Corp. Method and apparatus for use of porous implants
US8029575B2 (en) 2005-10-25 2011-10-04 Globus Medical, Inc. Porous and nonporous materials for tissue grafting and repair
EP1779812A1 (en) 2005-10-26 2007-05-02 Etervind AB An osseointegration implant
US8308807B2 (en) 2005-11-09 2012-11-13 Zimmer, Gmbh Implant with differential anchoring
EP1949989B1 (en) 2005-11-15 2012-01-11 Panasonic Electric Works Co., Ltd. Process for producing three-dimensionally shaped object
US8728387B2 (en) 2005-12-06 2014-05-20 Howmedica Osteonics Corp. Laser-produced porous surface
US7578851B2 (en) 2005-12-23 2009-08-25 Howmedica Osteonics Corp. Gradient porous implant
EP1803513B1 (en) * 2005-12-30 2017-03-29 Howmedica Osteonics Corp. Method of manufacturing implants using laser
US20070156249A1 (en) 2006-01-05 2007-07-05 Howmedica Osteonics Corp. High velocity spray technique for medical implant components
US9327056B2 (en) 2006-02-14 2016-05-03 Washington State University Bone replacement materials
US8147861B2 (en) * 2006-08-15 2012-04-03 Howmedica Osteonics Corp. Antimicrobial implant
US20080161927A1 (en) 2006-10-18 2008-07-03 Warsaw Orthopedic, Inc. Intervertebral Implant with Porous Portions
EP1961433A1 (en) 2007-02-20 2008-08-27 National University of Ireland Galway Porous substrates for implantation
WO2008104599A1 (en) 2007-02-28 2008-09-04 Cinvention Ag High surface cultivation system bag
ITUD20070092A1 (en) 2007-05-29 2008-11-30 Lima Lto S P A PROSTHETIC ELEMENT AND RELATIVE PROCEDURE FOR IMPLEMENTATION
US8066770B2 (en) 2007-05-31 2011-11-29 Depuy Products, Inc. Sintered coatings for implantable prostheses
JP2010528765A (en) 2007-06-07 2010-08-26 スミス アンド ネフュー インコーポレーテッド Reticulated particle porous coating for medical implant applications
WO2009014718A1 (en) 2007-07-24 2009-01-29 Porex Corporation Porous laser sintered articles
US20110076316A1 (en) 2007-10-08 2011-03-31 Sureshan Sivananthan Scalable matrix for the in vivo cultivation of bone and cartilage
CA2704032C (en) 2007-10-29 2016-10-18 Zimmer, Inc. Medical implants and methods for delivering biologically active agents
US8979938B2 (en) 2007-11-08 2015-03-17 Linares Medical Devices, Llc Artificial knee implant including liquid ballast supporting / rotating surfaces and incorporating flexible multi-material and natural lubricant retaining matrix applied to a joint surface
AU2009205896A1 (en) 2008-01-17 2009-07-23 Synthes Gmbh An expandable intervertebral implant and associated method of manufacturing the same
WO2009116950A1 (en) 2008-03-17 2009-09-24 Nanyang Polytechnic Mould for casting tissue engineering scaffolds and process for generating the same
GB0809721D0 (en) 2008-05-28 2008-07-02 Univ Bath Improvements in or relating to joints and/or implants
CN100588379C (en) 2008-06-26 2010-02-10 上海交通大学 Preparation of artificial joint prosthesis with partially controllable porous structure
US8696754B2 (en) 2008-09-03 2014-04-15 Biomet Manufacturing, Llc Revision patella prosthesis
KR20110090922A (en) 2008-10-29 2011-08-10 스미스 앤드 네퓨, 인크. Porous surface layers with increased surface roughness and implants incorporating the same
ES2555487T3 (en) 2008-12-18 2016-01-04 4-Web, Inc. Lattice lattice structure implant
US20110004447A1 (en) 2009-07-01 2011-01-06 Schlumberger Technology Corporation Method to build 3D digital models of porous media using transmitted laser scanning confocal mircoscopy and multi-point statistics
EP2253291B1 (en) 2009-05-19 2016-03-16 National University of Ireland, Galway A bone implant with a surface anchoring structure
WO2011022560A1 (en) 2009-08-19 2011-02-24 Smith & Nephew, Inc. Porous implant structures
US20110200478A1 (en) 2010-02-14 2011-08-18 Romain Louis Billiet Inorganic structures with controlled open cell porosity and articles made therefrom
IT1398443B1 (en) 2010-02-26 2013-02-22 Lima Lto S P A Ora Limacorporate Spa INTEGRATED PROSTHETIC ELEMENT
CA2802099A1 (en) 2010-06-08 2011-12-15 Smith & Nephew, Inc. Implant components and methods
US20110313532A1 (en) 2010-06-18 2011-12-22 Jessee Hunt Bone implant interface system and method
US9801974B2 (en) 2010-08-13 2017-10-31 Smith & Nephew, Inc. Patellar implants
US8727203B2 (en) 2010-09-16 2014-05-20 Howmedica Osteonics Corp. Methods for manufacturing porous orthopaedic implants
CN102087676B (en) 2010-12-13 2012-07-04 上海大学 Pore network model (PNM)-based bionic bone scaffold designing method
WO2013006778A2 (en) 2011-07-07 2013-01-10 4-Web, Inc. Foot and ankle implant system and method
US20130030529A1 (en) 2011-07-29 2013-01-31 Jessee Hunt Implant interface system and method
EP2773293B1 (en) 2011-11-03 2017-08-30 4-web, Inc. Implant for length preservation during bone repair
CA2863865C (en) 2012-02-08 2021-08-24 4-Web, Inc. Prosthetic implant for ball and socket joints and method of use
US9180010B2 (en) 2012-04-06 2015-11-10 Howmedica Osteonics Corp. Surface modified unit cell lattice structures for optimized secure freeform fabrication
US8843229B2 (en) 2012-07-20 2014-09-23 Biomet Manufacturing, Llc Metallic structures having porous regions from imaged bone at pre-defined anatomic locations
US9415137B2 (en) 2012-08-22 2016-08-16 Biomet Manufacturing, Llc. Directional porous coating
KR20150060828A (en) 2012-09-25 2015-06-03 4웹, 인코포레이티드 Programmable implants and methods of using programmable implants to repair bone structures
US20140288650A1 (en) 2013-03-15 2014-09-25 4Web, Inc. Motion preservation implant and methods
JP2016513551A (en) 2013-03-15 2016-05-16 マコ サージカル コーポレーション Unicondylar tibial knee implant
JP6573598B2 (en) 2013-03-15 2019-09-11 フォー−ウェブ・インコーポレイテッド Traumatic fracture repair system and method
US8983646B1 (en) 2013-10-10 2015-03-17 Barbara Hanna Interactive digital drawing and physical realization
US10842634B2 (en) 2014-05-02 2020-11-24 The Royal Institution For The Advancement Of Learning/Mcgill University Structural porous biomaterial and implant formed of same
US20150374882A1 (en) 2014-06-20 2015-12-31 Robert Anthony McDemus Porous material
US10881518B2 (en) 2017-04-01 2021-01-05 HD LifeSciences LLC Anisotropic biocompatible lattice structure
US11628517B2 (en) 2017-06-15 2023-04-18 Howmedica Osteonics Corp. Porous structures produced by additive layer manufacturing
US11071630B2 (en) 2017-11-09 2021-07-27 DePuy Synthes Products, Inc. Orthopaedic prosthesis for an interphalangeal joint and associated method

Patent Citations (101)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US14403A (en) * 1856-03-11 Improved spirit blow-pipe
US3605123A (en) * 1969-04-29 1971-09-20 Melpar Inc Bone implant
US3816855A (en) * 1971-06-01 1974-06-18 Nat Res Dev Knee joint prosthesis
US3806961A (en) * 1972-02-16 1974-04-30 Sulzer Ag Phosthetic patella implant
US4085466A (en) * 1974-11-18 1978-04-25 National Research Development Corporation Prosthetic joint device
US4202055A (en) * 1976-05-12 1980-05-13 Battelle-Institut E.V. Anchorage for highly stressed endoprostheses
US4164794A (en) * 1977-04-14 1979-08-21 Union Carbide Corporation Prosthetic devices having coatings of selected porous bioengineering thermoplastics
US4305340A (en) * 1978-02-24 1981-12-15 Yuwa Sangyo Kabushiki Kaisha Method of forming a box-shaped structure from a foldable metal sheet
US4218494A (en) * 1978-07-04 1980-08-19 Centro Richerche Fiat S.P.A. Process for coating a metallic surface with a wear-resistant material
US4385404A (en) * 1980-02-21 1983-05-31 J. & P. Coats, Limited Device and method for use in the treatment of damaged articular surfaces of human joints
US4344193A (en) * 1980-11-28 1982-08-17 Kenny Charles H Meniscus prosthesis
US4644942A (en) * 1981-07-27 1987-02-24 Battelle Development Corporation Production of porous coating on a prosthesis
US4502161A (en) * 1981-09-21 1985-03-05 Wall W H Prosthetic meniscus for the repair of joints
US4502161B1 (en) * 1981-09-21 1989-07-25
US4673408A (en) * 1983-08-24 1987-06-16 Arthroplasty Research & Development (Pty) Ltd. Knee prosthesis
US4969907A (en) * 1985-01-08 1990-11-13 Sulzer Brothers Limited Metal bone implant
US4714473A (en) * 1985-07-25 1987-12-22 Harrington Arthritis Research Center Knee prosthesis
US5034186A (en) * 1985-11-20 1991-07-23 Permelec Electrode Ltd. Process for providing titanium composite having a porous surface
US4636219A (en) * 1985-12-05 1987-01-13 Techmedica, Inc. Prosthesis device fabrication
US4714474A (en) * 1986-05-12 1987-12-22 Dow Corning Wright Corporation Tibial knee joint prosthesis with removable articulating surface insert
US4961154A (en) * 1986-06-03 1990-10-02 Scitex Corporation Ltd. Three dimensional modelling apparatus
US4719908A (en) * 1986-08-15 1988-01-19 Osteonics Corp. Method and apparatus for implanting a prosthetic device
US4944817A (en) * 1986-10-17 1990-07-31 Board Of Regents, The University Of Texas System Multiple material systems for selective beam sintering
US5616294A (en) * 1986-10-17 1997-04-01 Board Of Regents, The University Of Texas System Method for producing parts by infiltration of porous intermediate parts
US5017753A (en) * 1986-10-17 1991-05-21 Board Of Regents, The University Of Texas System Method and apparatus for producing parts by selective sintering
US4863538A (en) * 1986-10-17 1989-09-05 Board Of Regents, The University Of Texas System Method and apparatus for producing parts by selective sintering
US5155324A (en) * 1986-10-17 1992-10-13 Deckard Carl R Method for selective laser sintering with layerwise cross-scanning
US5076869A (en) * 1986-10-17 1991-12-31 Board Of Regents, The University Of Texas System Multiple material systems for selective beam sintering
US5386500A (en) * 1987-06-02 1995-01-31 Cubital Ltd. Three dimensional modeling apparatus
US5287435A (en) * 1987-06-02 1994-02-15 Cubital Ltd. Three dimensional modeling
US5735903A (en) * 1987-07-20 1998-04-07 Li; Shu-Tung Meniscal augmentation device
US5158574A (en) * 1987-07-20 1992-10-27 Regen Corporation Prosthetic meniscus
US5031120A (en) * 1987-12-23 1991-07-09 Itzchak Pomerantz Three dimensional modelling apparatus
US5080674A (en) * 1988-09-08 1992-01-14 Zimmer, Inc. Attachment mechanism for securing an additional portion to an implant
US4990163A (en) * 1989-02-06 1991-02-05 Trustees Of The University Of Pennsylvania Method of depositing calcium phosphate cermamics for bone tissue calcification enhancement
US5053090A (en) * 1989-09-05 1991-10-01 Board Of Regents, The University Of Texas System Selective laser sintering with assisted powder handling
US5192328A (en) * 1989-09-29 1993-03-09 Winters Thomas F Knee joint replacement apparatus
US5024670A (en) * 1989-10-02 1991-06-18 Depuy, Division Of Boehringer Mannheim Corporation Polymeric bearing component
US5004476A (en) * 1989-10-31 1991-04-02 Tulane University Porous coated total hip replacement system
US5067964A (en) * 1989-12-13 1991-11-26 Stryker Corporation Articular surface repair
US5171282A (en) * 1990-01-12 1992-12-15 Societe Civile D'innovations Technologique Femoral member for knee prosthesis
US5108432A (en) * 1990-06-24 1992-04-28 Pfizer Hospital Products Group, Inc. Porous fixation surface
US5702448A (en) * 1990-09-17 1997-12-30 Buechel; Frederick F. Prosthesis with biologically inert wear resistant surface
US5147402A (en) * 1990-12-05 1992-09-15 Sulzer Brothers Limited Implant for ingrowth of osseous tissue
US5323954A (en) * 1990-12-21 1994-06-28 Zimmer, Inc. Method of bonding titanium to a cobalt-based alloy substrate in an orthophedic implant device
US5176710A (en) * 1991-01-23 1993-01-05 Orthopaedic Research Institute Prosthesis with low stiffness factor
US5219362A (en) * 1991-02-07 1993-06-15 Finsbury (Instruments) Limited Knee prosthesis
US5314478A (en) * 1991-03-29 1994-05-24 Kyocera Corporation Artificial bone connection prosthesis
US5571185A (en) * 1991-10-12 1996-11-05 Eska Implants Gmbh Process for the production of a bone implant and a bone implant produced thereby
US5282870A (en) * 1992-01-14 1994-02-01 Sulzer Medizinaltechnik Ag Artificial knee joint
US5609646A (en) * 1992-01-23 1997-03-11 Howmedica International Acetabular cup for a total hip prosthesis
US5282861A (en) * 1992-03-11 1994-02-01 Ultramet Open cell tantalum structures for cancellous bone implants and cell and tissue receptors
US5496372A (en) * 1992-04-17 1996-03-05 Kyocera Corporation Hard tissue prosthesis including porous thin metal sheets
US5824102A (en) * 1992-06-19 1998-10-20 Buscayret; Christian Total knee prosthesis
US5648450A (en) * 1992-11-23 1997-07-15 Dtm Corporation Sinterable semi-crystalline powder and near-fully dense article formed therein
US5728162A (en) * 1993-01-28 1998-03-17 Board Of Regents Of University Of Colorado Asymmetric condylar and trochlear femoral knee component
US5368602A (en) * 1993-02-11 1994-11-29 De La Torre; Roger A. Surgical mesh with semi-rigid border members
US5358529A (en) * 1993-03-05 1994-10-25 Smith & Nephew Richards Inc. Plastic knee femoral implants
US5443510A (en) * 1993-04-06 1995-08-22 Zimmer, Inc. Porous coated implant and method of making same
US5443518A (en) * 1993-07-20 1995-08-22 Zimmer, Inc. Knee position indicator
US5398193A (en) * 1993-08-20 1995-03-14 Deangelis; Alfredo O. Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor
US5398193B1 (en) * 1993-08-20 1997-09-16 Alfredo O Deangelis Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor
US5549700A (en) * 1993-09-07 1996-08-27 Ortho Development Corporation Segmented prosthetic articulation
US5490962A (en) * 1993-10-18 1996-02-13 Massachusetts Institute Of Technology Preparation of medical devices by solid free-form fabrication methods
US5773789A (en) * 1994-04-18 1998-06-30 Bristol-Myers Squibb Company Method of making an orthopaedic implant having a porous metal pad
US5504300A (en) * 1994-04-18 1996-04-02 Zimmer, Inc. Orthopaedic implant and method of making same
US6049054A (en) * 1994-04-18 2000-04-11 Bristol-Myers Squibb Company Method of making an orthopaedic implant having a porous metal pad
US5973222A (en) * 1994-04-18 1999-10-26 Bristol-Myers Squibb Co. Orthopedic implant having a porous metal pad
US5795353A (en) * 1994-05-06 1998-08-18 Advanced Bio Surfaces, Inc. Joint resurfacing system
US6248131B1 (en) * 1994-05-06 2001-06-19 Advanced Bio Surfaces, Inc. Articulating joint repair
US5879387A (en) * 1994-08-25 1999-03-09 Howmedica International Inc. Prosthetic bearing element and method of manufacture
US5989472A (en) * 1994-10-05 1999-11-23 Howmedica International, Inc. Method for making a reinforced orthopedic implant
US5571196A (en) * 1994-10-24 1996-11-05 Stein; Daniel Patello-femoral joint replacement device and method
US5824098A (en) * 1994-10-24 1998-10-20 Stein; Daniel Patello-femoral joint replacement device and method
US5514183A (en) * 1994-12-20 1996-05-07 Epstein; Norman Reduced friction prosthetic knee joint utilizing replaceable roller bearings
US5879398A (en) * 1995-02-14 1999-03-09 Zimmer, Inc. Acetabular cup
US5782908A (en) * 1995-08-22 1998-07-21 Medtronic, Inc. Biocompatible medical article and method
US5776201A (en) * 1995-10-02 1998-07-07 Johnson & Johnson Professional, Inc. Modular femoral trial system
US5640667A (en) * 1995-11-27 1997-06-17 Board Of Regents, The University Of Texas System Laser-directed fabrication of full-density metal articles using hot isostatic processing
US5681354A (en) * 1996-02-20 1997-10-28 Board Of Regents, University Of Colorado Asymmetrical femoral component for knee prosthesis
US6087553A (en) * 1996-02-26 2000-07-11 Implex Corporation Implantable metallic open-celled lattice/polyethylene composite material and devices
US6046426A (en) * 1996-07-08 2000-04-04 Sandia Corporation Method and system for producing complex-shape objects
US6215093B1 (en) * 1996-12-02 2001-04-10 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Selective laser sintering at melting temperature
US6280478B1 (en) * 1997-03-04 2001-08-28 Implico B.V. Artefact suitable for use as a bone implant
US5928285A (en) * 1997-05-30 1999-07-27 Bristol-Myers Squibb Co. Orthopaedic implant having an articulating surface with a conforming and translational surface
US6355086B2 (en) * 1997-08-12 2002-03-12 Rolls-Royce Corporation Method and apparatus for making components by direct laser processing
US20010014403A1 (en) * 1997-08-12 2001-08-16 Lawrence Evans Brown Method and apparatus for making components by direct laser processing
US6190407B1 (en) * 1997-11-20 2001-02-20 St. Jude Medical, Inc. Medical article with adhered antimicrobial metal
US6139585A (en) * 1998-03-11 2000-10-31 Depuy Orthopaedics, Inc. Bioactive ceramic coating and method
US20020016635A1 (en) * 1998-05-14 2002-02-07 Hayes Medical, Inc. Implant with composite coating
US6261322B1 (en) * 1998-05-14 2001-07-17 Hayes Medical, Inc. Implant with composite coating
US6132468A (en) * 1998-09-10 2000-10-17 Mansmann; Kevin A. Arthroscopic replacement of cartilage using flexible inflatable envelopes
US6283997B1 (en) * 1998-11-13 2001-09-04 The Trustees Of Princeton University Controlled architecture ceramic composites by stereolithography
US6096043A (en) * 1998-12-18 2000-08-01 Depuy Orthopaedics, Inc. Epicondylar axis alignment-femoral positioning drill guide
US6395327B1 (en) * 1999-03-12 2002-05-28 Zimmer, Inc. Enhanced fatigue strength orthopaedic implant with porous coating and method of making same
US20020151983A1 (en) * 1999-03-12 2002-10-17 Shetty H. Ravindranath Enhanced fatigue strength orthopaedic implant with porous coating and method of making same
US6206927B1 (en) * 1999-04-02 2001-03-27 Barry M. Fell Surgically implantable knee prothesis
US6251143B1 (en) * 1999-06-04 2001-06-26 Depuy Orthopaedics, Inc. Cartilage repair unit
US6299645B1 (en) * 1999-07-23 2001-10-09 William S. Ogden Dove tail total knee replacement unicompartmental
US6206924B1 (en) * 1999-10-20 2001-03-27 Interpore Cross Internat Three-dimensional geometric bio-compatible porous engineered structure for use as a bone mass replacement or fusion augmentation device
US6371958B1 (en) * 2000-03-02 2002-04-16 Ethicon, Inc. Scaffold fixation device for use in articular cartilage repair

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110143094A1 (en) * 2009-12-11 2011-06-16 Ngimat Co. Process for Forming High Surface Area Embedded Coating with High Abrasion Resistance
US8834964B2 (en) * 2009-12-11 2014-09-16 Ngimat, Co. Process for forming high surface area embedded coating with high abrasion resistance
EP2817037B1 (en) * 2012-02-20 2022-08-03 Smith & Nephew, Inc. Methods of making porous structures
US20170021453A1 (en) * 2013-12-23 2017-01-26 General Electric Technology Gmbh Gamma prime precipitation strengthened nickel-base superalloy for use in powder based additive manufacturing process
US20150321289A1 (en) * 2014-05-12 2015-11-12 Siemens Energy, Inc. Laser deposition of metal foam
US11897033B2 (en) 2018-04-19 2024-02-13 Compagnie Generale Des Etablissements Michelin Process for the additive manufacturing of a three-dimensional metal part
US11167375B2 (en) 2018-08-10 2021-11-09 The Research Foundation For The State University Of New York Additive manufacturing processes and additively manufactured products
US11426818B2 (en) 2018-08-10 2022-08-30 The Research Foundation for the State University Additive manufacturing processes and additively manufactured products
WO2021097248A1 (en) * 2019-11-14 2021-05-20 University Of Washington Closed-loop feedback for additive manufacturing simulation

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